Connect public, paid and private patent data with Google Patents Public Datasets

Cardiac treatment system and method

Download PDF

Info

Publication number
US9421102B2
US9421102B2 US14053587 US201314053587A US9421102B2 US 9421102 B2 US9421102 B2 US 9421102B2 US 14053587 US14053587 US 14053587 US 201314053587 A US201314053587 A US 201314053587A US 9421102 B2 US9421102 B2 US 9421102B2
Authority
US
Grant status
Grant
Patent type
Prior art keywords
heart
implant
bladder
fillable
end
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active, expires
Application number
US14053587
Other versions
US20140107405A1 (en )
Inventor
Aaron Hjelle
William E. Cohn
Richard F. Schroeder
James F. Buck
Karl R. Leinsing
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Mardil Inc
Original Assignee
Mardil Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices
    • A61F2/2478Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
    • A61F2/2481Devices outside the heart wall, e.g. bags, strips or bands
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1008Tubes; Connections therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1037Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps
    • A61M1/1046Drive systems therefor, e.g. mechanically, electromechanically or skeletal muscle drive means
    • A61M1/106Drive systems therefor, e.g. mechanically, electromechanically or skeletal muscle drive means using hydraulic or pneumatic means
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1037Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps
    • A61M1/107Pulsating membrane pumps without valves, e.g. for counter pulsation, extra-arterial balloon pumps
    • DTEXTILES; PAPER
    • D04BRAIDING; LACE-MAKING; KNITTING; TRIMMINGS; NON-WOVEN FABRICS
    • D04BKNITTING
    • D04B21/00Warp knitting processes for the production of fabrics or articles not dependent on the use of particular machines; Fabrics or articles defined by such processes
    • D04B21/10Open-work fabrics
    • D04B21/12Open-work fabrics characterised by thread material
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/39Markers, e.g. radio-opaque or breast lesions markers
    • A61B2090/3966Radiopaque markers visible in an X-ray image
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices
    • A61F2/2478Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
    • A61F2/2481Devices outside the heart wall, e.g. bags, strips or bands
    • A61F2002/2484Delivery devices therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/95Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2002/9517Instruments specially adapted for placement or removal of stents or stent-grafts handle assemblies therefor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0003Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having an inflatable pocket filled with fluid, e.g. liquid or gas
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0096Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers
    • A61F2250/0098Markers and sensors for detecting a position or changes of a position of an implant, e.g. RF sensors, ultrasound markers radio-opaque, e.g. radio-opaque markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/1037Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps
    • A61M1/1067Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps using a blood vessel as flexible element
    • A61M1/1068Pumps having flexible elements, e.g. with membranes, diaphragms, or bladder pumps using a blood vessel as flexible element using the heart as flexible element
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/12Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps implantable into the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/10Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps
    • A61M1/12Blood pumps; Artificial hearts; Devices for mechanical circulatory assistance, e.g. intra-aortic balloon pumps implantable into the body
    • A61M1/122Heart assist devices, i.e. for assisting an ailing heart, using additional pumping means in the blood circuit
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/32General characteristics of the apparatus with radio-opaque indicia
    • DTEXTILES; PAPER
    • D10INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10BINDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
    • D10B2509/00Medical; Hygiene
    • D10B2509/08Hernia repair mesh

Abstract

Devices and methods for providing localized pressure to a region of a patient's heart to improve heart functioning, including: (a) a jacket made of a flexible biocompatible material, the jacket having an open top end that is received around the heart and a bottom portion that is received around the apex of the heart; and (b) at least one inflatable bladder disposed on an interior surface of the jacket, the inflatable bladder having an inelastic outer surface positioned adjacent to the jacket and an elastic inner surface such that inflation of the bladder causes the bladder to deform substantially inwardly to exert localized pressure against a region of the heart.

Description

CROSS-REFERENCE TO RELATED APPLICATION(S)

This application claims priority to U.S. Provisional Patent Application No. 61/713,351 filed on Oct. 12, 2012 by Hjelle et al., the contents of which are fully incorporated herein by reference.

TECHNICAL FIELD

The present disclosure relates to medical devices for treating heart diseases and valvular dysfunction, including valvular regurgitation.

BACKGROUND OF THE INVENTION

Various compression-style systems currently exist for treating heart diseases and conditions such as congestive heart disease and valvular dysfunction. These systems typically involve either: (a) jackets that are placed around the heart to limit heart expansion to treat congestive heart disease, or (b) bands that are placed around the heart with fillable chambers to exert localized pressure to re-form the shape of heart valves, for example to minimize valve leakage.

An example of the former is found in U.S. Published Patent Application 2010/0160721 entitled “Cardiac Support Device With Differential Compliance.” This device is used to treat congestive heart disease. Congestive heart disease is the progressive enlargement of the heart. This enlargement requires the heart to perform an increasing amount of work. In time, the heart cannot supply an adequate amount of blood, resulting in a patient that is fatigued and in discomfort. The cardiac support device of U.S. Application 2101/0160721 limits heart expansion using a flexible jacket positioned around the heart. An example of the second type of system is found in Mardil, Inc.'s U.S. Pat. No. 8,092,363 entitled “Heart Band With Fillable Chambers To Modify Heart Valve Function.” This device has fillable chambers that exert inward radial forces on heart valves. The fillable chambers are disposed within inner and outer layers of a silicone rubber band.

SUMMARY

Some embodiments described herein provide a system including an cardiac implant structure configured to be positioned around the exterior of an epicardial surface of a heart. Such a system can be used, for example, to treat various heart conditions, including but not limited to functional mitral regurgitation (“FMR”), tricuspid valve regurgitation, congestive heart failure, or a combination thereof. The implant structure can include a mesh body having a leading hem region configured to elastically flex and engage with an atrial-ventricular groove of the heart, and a fillable bladder mounted to the mesh body at a predetermined location so as to provide localized pressure at a targeted surface region of the heart spaced apart from the atrial-ventricular groove. The implant structure can be equipped with radiopaque markers at selected locations along the leading hem region, along or within the fillable bladder, or a combination thereof, so that the relative positioning of the implant structure and the targeted landmarks of the heart can be readily identified both during and after an implantation procedure. For example, in particular embodiments, the fillable bladder (equipped with markers along a periphery thereof) can be coupled to the mesh body at a specific location to exert a localized pressure on the posterior lateral surface of the heart to thereby deflect the “P2” portion of the posterior leaflet of the mitral valve to treat FMR. Accordingly, the combined components of the implant structure can be configured to apply supporting or deformation forces to multiple targeted regions of the heart in a manner that supports the ventricle walls of the heart, particular valve structures of the heart, and (optionally) the atrial-ventricular groove of the heart.

Additionally, some embodiments of a method for delivering the implant structure to the heart can be achieved in a minimally invasive manner that benefits both the clinician and the user. A delivery device can be operated by a surgeon or other clinician to advance the implant structure through a relatively small opening of a selected intercostal space before the implant structure expands over the apex, ventricles, and atrial-ventricular groove of the heart. In a particular embodiment, the implant structure can be pre-loaded on the delivery device and packaged in a sterilized kit so that the clinician can advantageously begin the implantation procedure without first having to load the implant device onto the delivery device. Also, the implant structure may optionally be loaded onto the delivery device in a predetermined relative position so that the fillable bladder has a predetermined orientation relative to a handle of the delivery device, thereby assisting the clinician in aligning the fillable bladder with the targeted surface region of the heart (e.g., along a posterior lateral surface of the heart in particular implementations). In some implementations of the method, the fillable bladder (when inflated) of the implant structure can be configured to expand inwardly toward the epicardial surface more so than it expands outwardly away from the heart.

Particular embodiments described herein include a cardiac implant including an implant body and a fillable bladder. The implant body can comprise a mesh material, and the implant body may include a leading end portion defining an open leading end and a trailing end portion defining an open trailing end of a diameter that is less than a diameter of the open leading end. The fillable bladder can be coupled to the implant body. Optionally, the cardiac implant may include one or more additional features described in more detail below.

Particular embodiments described herein include a cardiac implant for implantation around an exterior of a heart. The implant may include an implant body comprising a mesh material, which optionally is formed into a generally tubular configuration. The implant body may also include a leading end portion defining an open leading end and a trailing end portion defining an open trailing end of a diameter that is less than a diameter of the open leading end. The trailing end portion may have a length configured to extend proximal of the apex of the heart when the leading end portion is positioned in an atrial-ventricular groove of the heart. Further, the cardiac implant may optionally include a fillable bladder mounted to the implant body. The fillable bladder may be positioned relative to the open leading end such that, when the leading end portion is positioned in the atrial-ventricular groove, the fillable bladder is positionable on an exterior of a heart wall. Optionally, the cardiac implant may include one or more additional features described in detail herein.

In some embodiments, a cardiac implant for implantation around an exterior of a heart may include an implant body. The implant body can comprises a mesh material that, optionally, is formed into a generally tubular configuration. The implant body may define an open leading end and an open trailing end of a lateral width that is less than a lateral width of the open leading end. The implant body may include: a generally cylindrical leading end portion, a transition portion, and a generally cylindrical trailing end portion. The generally cylindrical leading end portion can define the open leading end of the implant body, and the leading end portion may have a lateral width and construction for positioning around an atrial-ventricular groove of the heart. The transition portion may extend proximally from the leading end portion and may be configured to circumferentially encompass ventricles of the heart. Optionally, the transition portion can have a greater diameter at its distal end than at its proximal end. The generally cylindrical trailing end portion may extend proximally from the transition portion and may have a length sized such that the trailing end portion extends proximal of the apex of the heart when the leading end portion is positioned around the atrial-ventricular groove. The cardiac implant may also include a fillable bladder coupled to the implant body. The fillable bladder can be positioned such that, when the leading end portion is positioned around the atrial-ventricular groove, the fillable bladder is positionable on an exterior of a heart wall adjacent to a heart valve structure. Optionally, the cardiac implant may further include one or more additional features described in detail herein.

In particular embodiments, a cardiac implant for implantation around an exterior of a heart can include an implant body comprising a jacket of mesh material configured for implantation circumferentially around ventricles of the heart. The jacket may an open leading end sized for positioning around an atrial-ventricular groove of the heart. The implant body may also include a hem located around a perimeter of the open leading end. The hem may be formed from a portion of the mesh material and an elastic band surrounded by the portion of the mesh material. Optionally, the circumferential length of the elastic band may be less than the circumferential length of the portion of the mesh material surrounding the elastic band. The elastic band and the portion of the mesh material surrounding the elastic band can have compliances selected such that the hem holds the hem of the implant body in place in the atrial-ventricular groove without interfering with cardiac blood vessel function in the region of the atrial-ventricular groove. Also, the cardiac implant may optionally include a fillable bladder attached on an inside of the mesh jacket. The fillable bladder may be positioned such that, when the implant is implanted with the hem positioned around the atrial-ventricular groove, the fillable bladder is positionable on an external heart wall adjacent to a targeted heart valve structure. The fillable bladder may include an inner layer and an opposing outer layer. The inner layer, when the hem positioned around the atrial-ventricular groove, can be adjacent to the external heart wall. The opposing outer layer may be adjacent to the mesh jacket. The inner layer of the fillable bladder can have a compliance that is greater than a compliance of the outer layer such that, when the bladder is inflated, the inner layer of the bladder extends more inwardly than the outer wall extends outwardly. Optionally, the cardiac implant may include one or more additional features described in detail herein.

Some embodiments described herein include a cardiac implant for implantation around an exterior of a heart. The cardiac implant may include a mesh jacket positionable circumferentially around an exterior the heart. Also, the cardiac implant may include a fillable bladder mounted to the mesh jacket. The fillable bladder can include an inner bladder layer and outer bladder layer. The inner bladder layer can be positioned with respect to the mesh jacket so that the inner bladder layer is adjacent to a targeted exterior surface of the heat when the mesh jacket is positioned around the exterior of the heart. The outer bladder layer can be positioned opposite from the inner bladder layer. Optionally, the inner bladder layer may have a compliance that is greater than a compliance of the outer bladder layer such that, when the mesh jacket is positioned around the exterior of the heart, the bladder expands more inwardly toward the targeted exterior surface of the heart than the bladder expands outwardly from the heart. Further, the cardiac implant may optionally include one or more additional features described in detail herein.

Further embodiments described herein include a cardiac implant system. The system may include a cardiac implant configured to be implanted around an exterior of the heart. The cardiac implant can include an implant body, an inflatable bladder attached to the implant body, and flexible tubing in fluid communication with an internal chamber of the inflatable bladder for inflating and deflating the inflatable bladder. The system may optionally include biocompatible ligation clips configured to attach to a proximal portion of the flexible tubing so as to seal an internal lumen of the flexible tubing. In some aspects, the ligation clips are configured to reside in an intercostal space while maintaining a selected inflation state of the inflatable bladder. Optionally, the cardiac implant system may include one or more additional features described in detail herein.

In various embodiments, a cardiac implant can include a mesh jacket, a fillable bladder, and one or more radiopaque markers. The mesh jacket may be configured to circumferentially extend around an exterior portion of the heart. The fillable bladder can be attached on an interior side of the mesh jacket. The fillable bladder may be positioned relative to a leading end of the mesh jacket such that, when the mesh jacket circumferentially extends around the exterior portion of the heart, the fillable bladder is positionable against an external heart wall adjacent to the a targeted valve structure. The fillable bladder may include an inner layer configured to engage with the external heart wall, and an outer layer positioned between the inner layer and the mesh jacket. The one or more radiopaque markers can be attached to an exterior side of the mesh jacket at a location wherein the fillable bladder is on an opposite side of the mesh jacket from the one or more radiopaque markers. Optionally, the cardiac implant may include one or more additional features described in detail herein.

Other embodiments described herein include a delivery system for delivering an implantable cardiac device. The delivery system may include an elongate barrel, a plurality of elongate members, a control mechanism, and a handle assembly. The plurality of elongate members may be configured to extend along a length of the elongate barrel and extend distally from the elongate barrel. Also, the plurality of elongate members may be advanceable distally with respect to the elongate barrel. Each of the elongate members can include a distal end for attachment to a cardiac implant configured to be implanted around an exterior of a heart. The control mechanism can be configured to extend and retract the plurality of elongate members relative to the elongate barrel. The handle assembly may optionally include a pistol grip configured to be held by a first hand of an operator while the operator uses a second hand to operate the control mechanism for the extension and refraction of the plurality of elongate members. Optionally, the delivery system may include one or more additional features described in detail herein.

Some embodiments described herein include a cardiac treatment system including a delivery system and a cardiac implant releasably mounted onto the delivery system. The delivery system may include an implant delivery mechanism comprising a plurality of distally extending elongate members each having a distal end portion configured for attachment to the cardiac implant. Also, the delivery system may include a proximal handle assembly. The proximal handle assembly can include a pistol grip configured to be held by one hand of an operator during a procedure to implant the cardiac implant. The pistol grip can extend in a first radial position from a longitudinal axis of the delivery system. The cardiac implant may include an implant body configured for implantation around external portions of a heart. The implant body can include a leading end portion defining an open leading end and being configured to advance over an apex of the heart. The leading end portion may be detachably attached to the distal end portions of the elongate members. The cardiac implant may also include a fillable bladder attached to the implant body. In particular implementations, the implant body may be mounted onto the delivery device in a second radial position from the longitudinal axis such that an orientation of the fillable bladder relative to the first radial position of the pistol grip of the handle aligns the fillable bladder with a targeted exterior portion of the heart (when the pistol grip of the handle is held by the one hand of the operator during the procedure to implant the cardiac implant). Optionally, the cardiac treatment system may include one or more additional features described in detail herein.

Further embodiments described herein include a method of treating heart valve insufficiency. The method may include introducing a cardiac device into a patient. The cardiac device can include an implant body comprising a mesh material and configured to surround at least a portion of the patient's heart. Also, the cardiac device may include a fillable bladder mounted to the implant body. The method may optionally include positioning one or more radiopaque markers of the fillable bladder at a targeted exterior region of the patient's heart that is adjacent to a targeted valve structure. Additionally, the method may optionally include one or more additional features described in detail herein.

In some embodiments, a method of treating heart valve insufficiency includes introducing a cardiac implant into a patient. The cardiac implant may include an implant body, which can optionally be formed into a generally tubular configuration. The implant body may include a leading end portion with an open leading end and a trailing end portion with an open trailing end. The cardiac implant may also include a fillable bladder attached to the implant body. The method may also include positioning the cardiac implant along an exterior of the heart so that the leading end portion is positioned in an atrial-ventricular groove of the heart, the trailing end portion of the implant extends proximal of the apex of the heart, and the fillable bladder positioned adjacent a targeted exterior surface of the heart that is adjacent to selected valve structure. The method may optionally include closing the open trailing end of the trailing end portion of the implant body so that the implant body encompasses the apex of the heart. Optionally, the method may include one or more additional features described in detail herein.

In particular embodiments, a method includes introducing a cardiac implant into a patient, wherein the cardiac implant may include an implant body and a fillable bladder. The implant body may include a jacket of mesh material and a hem located around a perimeter of an open leading end of the implant body. Optionally, the hem may be formed from a portion of the mesh material and an elastic band surrounded by the portion of the mesh material. The fillable bladder can be attached on an interior of the mesh jacket. The fillable bladder may include an inner layer and an adjacent outer layer that is adjacent the mesh jacket. The inner layer may have a compliance that is greater than a compliance of the outer layer. The method may also include positioning the cardiac implant within the pericardium and external to the epicardium of a heart. Such positioning may occur so that the hem of the implant is positioned in an atrial-ventricular groove of the heart and the fillable bladder is positioned adjacent a portion of external heart wall that is adjacent to selected valve structure. The method may further include filling the fillable chamber whereupon the inner layer expands inwardly to apply localized pressure against the portion of the external heart wall that is adjacent the selected valve structure. Optionally, the method may include one or more additional features described in detail herein.

In some embodiments, a method may include introducing a cardiac implant into a patient. The cardiac implant may include an implant body and a fillable bladder mounted to the implant body. The fillable bladder may include an inner bladder layer having a compliance that is greater than a compliance of the outer bladder layer. Also, the method may include positioning the cardiac implant within the pericardium and around the epicardium of a heart so that the inner bladder layer of the fillable bladder is positioned adjacent a portion of external heart wall that is adjacent selected valve structure. The method may include filling the fillable chamber such that the bladder expands more inwardly toward the heart than outwardly away from the heart and applies localized pressure on the external heart wall. Optionally, the method may include one or more additional features described in detail herein.

Further embodiments described herein include a method for an operator to implant a cardiac implant for treating heart valve insufficiency. The method may include providing a delivery system loaded with a cardiac implant. The cardiac implant may include an open leading end and configured for implantation around external portions of a heart. The delivery system may include an implant delivery mechanism comprising a plurality of distally extending elongate members each having a distal end portion attached to a portion of the cardiac implant at or near the open leading end. The delivery system may further include a proximal handle assembly comprising a pistol grip. Also, the delivery system may include a control mechanism configured in relation to the plurality of elongate members for manually extending the plurality of elongate members relative to the handle assembly. The method may include implanting the cardiac implant with the operator holding the pistol grip of the handle assembly in a first hand, and using a second hand to actuate the control mechanism to extend manually the plurality of elongate members to advance the open leading end of the cardiac implant over and past the apex of the heart to position the cardiac implant around external portions of the heart. Optionally, the method may include one or more additional features described in detail herein.

Various embodiments described herein include a method of treating heart valve insufficiency. The method may include providing a cardiac implant including an implant body, an inflatable bladder arranged on the implant body, and flexible tubing in fluid communication with an internal chamber of the inflatable bladder. The method may also include implanting the cardiac implant around external portions of the heart with the inflatable bladder positioned adjacent a portion of an external heart wall that is adjacent to a targeted heart valve structure. Further, the method may include inflating the inflatable bladder using the flexible tubing. Optionally, the method may include attaching at least one biodegradable ligation clip to a proximal portion of the flexible tubing to seal an internal lumen of the flexible tubing to maintain a selected inflation state of the fillable bladder. Also, the method may optionally include one or more additional features described in detail herein.

Particular embodiments described herein include a method of making a cardiac implant. The method may provide a cardiac implant for implantation around an exterior of a heart. The method may include providing a first plate structure having opening structure on a surface thereof. The opening structure may accommodate adhesive radiopaque material. The method may also include providing a second plate structure having two fillable bladder sheet components positioned thereon. Further, the method may include positioning, to provide a cardiac implant pre-assembly, a portion of a mesh jacket between the first plate structure and the two fillable bladder sheet components positioned on the second plate structure. The method may also include curing the implant pre-assembly to attach the radiopaque marker material, provided through the opening structure, on one side of the portion of the mesh jacket and the two fillable bladder sheet components on an opposite side of the portion of the mesh jacket. Optionally, the opening structure of the first plate structure may include at least one indentation in the first plate structure into which the adhesive radiopaque material is provided. In another option, the opening structure may include at least one hole through the first plate structure through which hole adhesive radiopaque material is provided. Optionally, the method may include one or more additional features described in detail herein.

These and other embodiments described herein may provide one or more of the following benefits. First, some embodiments include an implant structure having a combination of components that operate to contemporaneously apply forces for supporting or deformation different targeted regions of the heart. For example, the implant structure of particular embodiments of the system described can be configured to contemporaneously apply a localized pressure to a defined area of the posterior lateral surface of the heart while also applying a restraining force of to the ventricle walls of the heart and (optionally) a compressive supporting force to the atrial-ventricular groove of the heart.

Second, some embodiments of the system or method described herein can be used to treat various heart conditions, including but not limited to functional mitral valve regurgitation (“FMR”), tricuspid valve regurgitation, congestive heart failure, or a combination thereof. Upon implantation, implantation structure can apply forces for supporting or deformation regions of the heart in a manner that eliminates or reduces the symptoms of these conditions and that improves blood flow from the heart.

Third, some embodiments of the system or method described herein can include a delivery device configured to advantageously advanced the implant structure to the heart through a relatively small opening of a selected intercostal space proximate to the apex of the heart. Optionally, each delivery device can be configured as a disposable, single-use instrument that is pre-loaded with the implant structure and packaged in a sterilized kit. As such, the clinician can simply select a delivery device bearing the selected size of implant structure (pre-installed on a barrel of the delivery device by during manufacture or assembly) from a plurality of delivery devices in a hospital inventory. After the implant structure in implanted, the delivery device can be conveniently discarded along with other disposables from the operating room.

Fourth, in some embodiments, the implant structure can be arranged on the delivery device in a predetermined orientation relative to the handle of the delivery device. In such circumstances, the fillable bladder of the implant structure may be predisposed for advancement along a targeted side of the heart (e.g., a posterior side) when the handle of the delivery device is held in a selected position external to the opening in the chest, thereby assisting the clinician in aligning the fillable bladder with the targeted surface region of the heart.

Fifth, in particular embodiments, the implant structure can be equipped with radiopaque markers positioned at an advantageous combination of locations along the leading end, along the fillable bladder, or both. As such, during use of the implant structure, the relative positioning of the implant structure and the targeted landmarks of the heart can be readily identified both during and after an implantation procedure.

The details of one or more embodiments of the invention are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of such embodiments will be apparent from the description and drawings, and from the claims.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is an exploded view showing an implant for treating a heart and the heart upon which the implant may be implanted, in accordance with some embodiments.

FIG. 1B is a perspective cutaway view of a heart with the implant of FIG. 1A implanted on the heart.

FIG. 2A is a perspective side view of an implant for treating a heart, in accordance with some embodiments.

FIG. 2B is a perspective end view of the implant of FIG. 2A showing a fillable bladder in a deflated configuration.

FIG. 2C is a perspective end view of the implant of FIG. 2A showing the fillable bladder in an inflated configuration.

FIG. 3 is an exploded view of a fillable bladder, in accordance with some embodiments.

FIG. 4A is a perspective view of another implant for treating a heart that is positioned on a patient's heart, in accordance with some embodiments.

FIG. 4B is a perspective view of another implant for treating a heart including three optional bladder locations at the mitral valve, papillary muscle and tricuspid valve, in accordance with some embodiments.

FIG. 5 is a sectional elevation view through one of the inflatable bladders of FIGS. 4A and 4B.

FIG. 6A is a perspective side view of an implant delivery device that is loaded with an implant, in accordance with some embodiments.

FIG. 6B is a perspective side view of the implant delivery device of FIG. 6A with a heart stabilizer in an extended position.

FIG. 6C is a distal end view of the implant delivery device of FIG. 6A.

FIG. 7 is a front view of a low friction (e.g., lubricious) strip component for use with the implant delivery device of FIG. 6A, in accordance with some embodiments.

FIGS. 8A-8E are multiple perspective views of an implant delivery device with the heart stabilizer in an extended position, in accordance with some embodiments.

FIG. 8F is a perspective view of the implant delivery device of FIGS. 8A-8E, with the heart stabilizer in a retracted position.

FIG. 8G is a perspective view of the implant delivery device of FIGS. 8A-8E, with the heart stabilizer in a retracted position and multiple elongate actuator arms in fully extended positions.

FIG. 9A shows a perspective view of the implant delivery device of FIGS. 8A-8E, with one of its elongate arms in a partially extended position.

FIG. 9B is a partial perspective and partial cross-sectional view of the implant delivery device of FIG. 9A, the cross section taken along lines 9B shown in FIG. 9A.

FIG. 9C is a view of a proximal portion of the implant delivery device of FIGS. 9A-9B.

FIG. 10 is a perspective view of an actuator arm retainer ring component of the implant delivery device of FIG. 9A, in accordance with some embodiments.

FIG. 11A is a perspective view of an implant delivery device with an elongate arm in an implant released position that enables the release of an implant from the elongate arm, in accordance with some embodiments.

FIG. 11B is a perspective view of the implant delivery device of FIG. 11A with the elongate arm in an implant clamping position, in accordance with some embodiments.

FIGS. 12A-12C is a three-part flowchart of an example method for installing an implant in a patient to treat a heart condition, in accordance with some embodiments.

FIGS. 13A and 13B are top and perspective view of a device for facilitating an open surgical access passageway to the patient's heart, in accordance with some implementations of the method of FIGS. 12A-12C.

FIG. 13C is a perspective view of multiple ones of the device of FIGS. 13A and 13B in use on a patient, in accordance with some implementations of the method of FIGS. 12A-12C.

FIGS. 14A-14C are perspective top and side views of a device for measuring the size of a heart within the patient, in accordance with some implementations of the method of FIGS. 12A-12C.

FIG. 15 is a perspective view of the introduction into a patient's chest cavity of an implant that is loaded on an implant delivery device, in accordance with some implementations of the method of FIGS. 12A-12C.

FIGS. 16A-16C are perspective views of the advancement of an implant onto the patient's heart, in accordance with some implementations of the method of FIGS. 12A-12C.

FIG. 17 is a perspective view of the withdrawal of an implant delivery device after installing an implant on the patient's heart, in accordance with some implementations of the method of FIGS. 12A-12C.

FIG. 18 is a perspective view of trimming of the implant after installing an implant on the patient's heart, in accordance with some implementations of the method of FIGS. 12A-12C.

DETAILED DESCRIPTION OF ILLUSTRATIVE EMBODIMENTS

Referring to FIGS. 1A-1B, some embodiments of a system or method described herein include an implant structure configured to be positioned around the exterior of an epicardial surface of a heart H. Such an implant 100 can be used, for example, to treat various heart conditions, including but not limited to FMR, tricuspid valve regurgitation, congestive heart failure, or a combination thereof. For example, in the embodiment depicted in FIG. 1B, the implant 100 can include a fillable bladder 120 coupled to a mesh body 110 at a specific location to exert a localized pressure on the posterior lateral surface of the heart H to thereby deflect the “P2” portion of the posterior leaflet of the mitral valve to treat FMR. The combined components of the implant 100 can be configured to apply supporting or deformation forces to multiple targeted regions of the heart H in a manner that supports the ventricle walls of the heart, particular valve structures of the heart, and (optionally) atrial-ventricular groove of the heart. In use, the implant 100 can be delivered to the heart H through a relatively small opening of a selected intercostal space and thereafter expanded over the apex, ventricles, and atrial-ventricular groove of the heart. In some embodiments, a delivery device (described in detail below) can be operated by a clinician to install the implant 100 on the beating heart H at a selected location, which is verified in real time by the clinician in real using radiopaque markers positioned at an advantageous combination of locations along a hem 113 of the leading end, along the fillable bladder 120, or both.

Referring to FIG. 1A, an implant 100 can be positioned around the external surface of a heart H (e.g., external to the epicardium) to treat various heart conditions. Such heart conditions can include, but are not limited to, functional mitral regurgitation (“FMR”), tricuspid valve regurgitation, and congestive heart failure. FMR is a condition in which the valve structures are normal but the heart is in an abnormal configuration (e.g., an enlarged heart) wherein valve functioning is degraded or not optimal. The implant 100 in this embodiment has a tubular shape that defines an interior space. The implant 100 can be installed onto the heart H such that a portion of the heart H is positioned within the interior space defined by the implant 100. For example, in some implementations the implant 100 is installed so that some or all of the left and right ventricles of the heart H are positioned within the interior space defined by the implant 100. In such an arrangement, the implant 100 surrounds a perimeter of a portion of the heart H. Hence, the implants provided herein, of which implant 100 is one example, may also be referred to herein as jackets. In the depicted embodiment, the implant 100 is of a flexible or expandable tubular design in that it has an open distal end 112 and an open proximal end 119. The open distal end 112 of the implant 100 enables the implant 100 to be implanted by advancing the open distal end 112 around the heart from an inferior (apex) end of the heart to, for example, an atrial-ventricular groove of the heart (described below in connection with FIG. 1B). The open proximal end 119 of the implant 100 is present in the depicted embodiment to accommodate a minimally invasive delivery device (described below in connection with FIGS. 6A-6C) with one or more members that extend through the open proximal end 119 and attach to the open proximal end 119 of the implant 100 so as to push the distal end 112 of the implant 100 over and beyond the apex of the heart H and into, for example, the atrial-ventricular grove, as will be shown and described below.

In some embodiments, the implant 100 can include a tubular mesh body 110. The tubular mesh body 110 may include one or more seams 111 that are formed as a result of the construction of the tubular mesh body 110. For example, the one or more seams 111 may be formed as a result of making the mesh body 110 into a tube, as a result of creating contours within the mesh body 110, or as a result of creating hemmed ends of the mesh body 110. However, seams are not a requirement in all embodiments of the implant described herein. That is, in some alternative embodiments, the implant can be made with a seamless construction.

Still referring to FIG. 1A, a fillable bladder 120 is attached to the mesh body 110. The fillable bladder 120 may also be referred to herein as an inflatable bladder. In this embodiment, the fillable bladder 120 is affixed on an interior surface of the mesh body 120. Hence, when the implant 100 is installed onto the heart H (e.g., between the pericardium and epicardium), the fillable bladder 120 is positioned adjacent to and makes contact with the external surface of the heart H. In some alternative embodiments, the fillable bladder 120 can be affixed on the exterior of the mesh body 110, or installed in or between layers of material of a multi-layered mesh body. In further alternative embodiments, multiple fillable bladders 120 are affixed on a single mesh body 120.

An inflation tube 130 is in fluid communication with the fillable bladder 120. As described further herein, the inflation tube 130 provides a lumen through which an inflation fluid (e.g., saline or another biocompatible liquid) is transferred to thereby inflate or deflate the fillable bladder 120. In some embodiments, one or more ligation clips 140 are used to seal the inflation tube 130 after the fillable bladder 120 has been filled with an inflation fluid to a desired extent. As an alternative to the ligation clips 140, the inflation tube 130 can be doubled over to seal the inflation tube 130, and the configuration can be secured by tightly wrapping the doubled-over portion with a suture. In another alternative, a plug can be inserted into the end of the inflation tube 130. Other techniques and a combination of techniques can also be used to seal the proximal region of inflation tube 130. With the one or more ligation clips 140 installed on the inflation tube 130, the selected amount of inflation fluid can be maintained within the fillable bladder 120. With the fillable bladder 120 thusly inflated, the expansion of the bladder 120 causes a localized pressure to be applied to a selected exterior surface of the heart H (e.g., along an exterior of the epicardium), to thereby treat a heart condition.

The implant 100 can also include a plurality of radiopaque markers 115 and 125 in selected locations that provide a number of benefits to a surgeon during and after implantation. Such radiopaque markers 115 and 125 can facilitate radiographical visualization of the implant 100 during a minimally invasive implantation process. For example, in some instances the implant 100 is installed with the assistance of fluoroscopy. Other imaging modalities may also be used, such as echocardiography, MRI, and the like. Using imaging systems in conjunction with radiopaque markers 115 and 125, the implant 100 can be positioned onto the heart H, and oriented in relation to anatomical features of the heart H, as desired. In some implant procedures, contrast agent solutions are injected into the heart, or within the pericardial space, to enhance the radiographical visualization of anatomical features of the heart H on which an implant 100 is to be installed. The radiopaque markers 115 and 125 can comprise materials such as, but not limited to, tantalum, platinum, tungsten, palladium alloys, and the like.

In the embodiment shown, a first group of radiopaque markers 115 are positioned at a leading end 112 of the mesh body 110. The leading end 112 in this embodiment includes a circumferential hem region that defines the distal end opening 117 (refer to FIG. 2A). As described further herein, in some embodiments the radiopaque markers 115 are used to facilitate the installation of the implant 100 in relation to the heart H such that the leading end 112 is positioned in the atrial-ventricular groove of the heart H. A second group of radiopaque markers 125 are positioned on the implant 100 to identify the location of the fillable bladder 120 on the mesh body 110. For example, the second group of markers 125 can be mounted along at least a portion of a periphery of the fillable bladder 120. Using the radiopaque markers 125, the fillable bladder 120 can be positioned at a target location on the exterior surface of the heart H. For example, as will be described further herein, in some instances the fillable bladder 120 may be configured for installation at a selected position on the surface of the heart H (for example, on a posterior wall of the heart adjacent the mitral valve) so that the fillable bladder 120 will exert a localized pressure to induce the reshaping of a portion of the heart H when the fillable bladder 120 is inflated. In the case of positioning on a posterior wall of the heart adjacent the mitral valve, the fillable bladder 120 provides localized pressure that in turn is applied to a posterior portion of the mitral valve annulus, thus bringing the leaflets of the valve into closer proximity with one another and addressing a mitral valve regurgitation problem (described, for example, in more detail below in connection with FIG. 1B). While this embodiment includes the radiopaque markers 115 and 125 located near the leading end 112 and fillable bladder 120 respectively, in other embodiments radiopaque markers may be included at other locations instead of, or in addition to, the locations of the radiopaque markers 115 and 125.

Still referring to FIG. 1A, the mesh body 110 of the implant 100 also includes a trailing end portion 118 that is located opposite of the leading end 112. The trailing end portion 118 may also be referred to herein as the proximal region. The trailing end portion 118 can provide the implant 100 with an axial length such that, when the implant 100 is installed on the heart H, excess mesh material extends proximally away from the apex A of the heart H. As described in detail below, after installing the implant 100 onto the heart H, an excess length portion of the trailing end portion 118 can be optionally trimmed off of the implant 100. Thereafter, in some implementations the trimmed end of the mesh body 110 at the trailing end portion 118 is gathered or cinched around the apex A and closed using one or more sutures, clips, or the like. This implementation of providing a post-installation closure to the trimmed end of the mesh body 120 may be preferred in some cases, for example, to prevent the proximal end of the implant 100 from migrating, after implantation, distally toward the distal end of the implant 100, which may otherwise occur given the movement of the heart and the lesser degree anchoring of the implant 100 immediately after installation (before fibrosis and tissue ingrowth between the implant 100 and the heart tissue such as the epicardium, pericardium, or both).

Referring now to FIG. 1B, the implant 100 can be installed on the heart H so as to surround an inferior portion of the heart H, including at least a portion of the left and right ventricles V. In some embodiments, at least a portion of the leading end 112 is positioned in the atrial-ventricular groove of the heart H. By positioning the leading end 112 in the atrial-ventricular groove AV, the implant 100 can maintain a desired positioning in relation to the heart H by taking advantage of the contours of the heart H. In this embodiment, the implant 100 is installed in the pericardial cavity. That is, during the implantation process, the pericardium is opened and the implant 100 is installed over an exterior of the epicardium of the heart H and internal to the pericardium of the heart H. Thereafter, the pericardium is closed to thereby contain the implant 100 in the pericardial cavity. Over time, a fibrosis or tissue ingrowth process may occur to cause the mesh body 110 to be anchored to the epicardium, the pericardium, or a combination thereof. Optionally, in some instances, one or more sutures may be used to attach the mesh body 110 to the epicardium at the time of implantation.

In the depicted embodiment, the fillable bladder 120 is attached to an interior surface of the mesh body 110 such that, when the implant 100 is implanted, the fillable bladder 120 is positioned between the mesh body 110 and the heart H. In other words, a surface of the fillable bladder 120 is in direct contact with a surface of the heart H (e.g., an exterior epicardial surface in this embodiment). When an inflation fluid is supplied under pressure into the fillable bladder 120 (e.g., from a syringe device coupled to the inflation tube 130), the fillable bladder 120 expands from a collapsed condition to an operative condition to thereby exert a localized pressure to a targeted portion of the surface of the heart H. A target location for applying the localized pressure can be strategically selected to induce a desired effect to the patient's heart H. For example, as shown, a localized pressure can be exerted at a location on the heart H that causes a deflection to an annulus of a heart valve HV, such as a mitral valve or a tricuspid valve. In that manner, some types of valvular regurgitation can be treated. In a particular example, the fillable bladder 120 can be positioned to exert a localized pressure on the posterior lateral surface of the heart H to thereby deflect the “P2” portion of the posterior leaflet of the mitral valve to treat FMR. In another example, other areas on the exterior surface of the ventricles V can be targeted for the exertion of a localized pressure from the fillable bladder 120. In some such examples, the papillary muscles P are advantageously deflected. In certain instances, such deflecting of the papillary muscles P, and the chordae tendineae CT confluent therewith, can also treat valvular regurgitation.

While the examples of FIGS. 1A and 1B depict an implant 100 having a single fillable bladder 120, it should be understood that in other embodiments two or more fillable bladders may be included on a single implant device. In the depicted embodiment, the fillable bladder 120 is pre-attached to the mesh body 110. In some embodiments, one or more fillable bladders are separate from the mesh body, and are attached to the mesh body or positioned at a desired location inside the mesh body during the implantation procedure either before or after the mesh body has been installed on the heart. For example, the mesh body may be installed on the heart H of a patient, and subsequently one or more fillable bladders can be positioned at target locations in relation to the mesh body and then optionally attached to the mesh body in situ.

In some embodiments, the mesh body 110 is sized to snugly fit on the heart H, but not so tight as to cause a significant increase in left ventricular pressure during diastole or obstructions to the coronary arteries or other vessels such as the coronary sinus. That is, in these embodiments, the mesh body 110 is designed to be highly compliant to the shape of the heart H, and adaptable to gently conform with the distension of the myocardium as the heart H performs pumping actions.

Referring to FIGS. 2A-2C, the implant 100 of FIG. 1 will now be described in greater detail. FIG. 2A provides a perspective view illustrating the tubular shape and other features of the implant 100. FIGS. 2B and 2C provide end perspective views to illustrate, for example, the interior surfaces of the implant 100 and the fillable bladder 120. For instance, FIG. 2B depicts the fillable bladder 120 in a deflated configuration, while FIG. 2C depicts the fillable bladder 120 in an inflated configuration.

In some embodiments, the material of the mesh body 110 is constructed from a knitted, biocompatible material. In particular embodiments, the knitted material is made using a construction known as “Atlas knit.” The Atlas knit is a knit of fibers having directional expansion properties. More specifically, the knit, although formed of generally inelastic fibers, permits a construction of a flexible fabric at least slightly expandable beyond a rest state. The fibers of the mesh fabric are woven into two sets of fiber strands. The strands are interwoven to form the fabric with a first set of strands generally parallel and spaced-apart and with a second set of strands generally parallel and spaced-apart. For purposes of illustration in FIGS. 2A-2C, the mesh fabric is schematically shown herein as a diamond-shaped open cell mesh fabric having diagonal axes, but it should be understood from the description herein that the mesh fabric may have a different appearance. FIGS. 1A and 2A illustrates the knit mesh body 110 in a generally unexpanded state, whereas FIG. 1B illustrates the knit mesh body 110 is an expanded state. In some embodiments, the mesh body 110 is made of a Denier polyester. In other embodiments, the mesh body 110 can be made of other suitable biocompatible materials including polytetrafluoroethylene (PTFE), expanded PTFE (ePTFE), polypropylene, stainless steel, and the like, or combinations thereof. Other types of knitting processes can also be used to construct the implants provided herein. Further, other construction techniques in addition to knitting are envisioned. For example, some or all parts of the body 110 may be woven, braided, made of tubing or an expanded tubing, and the like.

In some embodiments, the mesh body 110 includes a leading end portion 114, a transition portion 116, and a trailing end portion 118. Each of the three portions 114, 116, and 118 are tubular. That is, the mesh material used to construct the portions 114, 116, and 118 is arranged to define open interior spaces. In this embodiment, the mesh body 110 is configured to provide a cross-section shape (e.g., perpendicular to a central axis of the implant 100) that is circular in each of the three portions 114, 116, and 118, and the portions 114 and 118 may be generally cylindrical along a majority of their respective axial lengths. In other embodiments, the materials can be arranged to define other cross-sectional shapes. In other embodiments, other configurations of implant body shapes are envisioned, and such portions 114, 116, and 118 are not necessarily implemented in all embodiments described herein. In some embodiments, the construction of the mesh body 110 may include one or more seams 111 as a result of sewing the mesh material into the desired shape. In some embodiments, the construction of the mesh body 110 may be seamless.

Still referring to FIGS. 2A-2C, in this embodiment, the generally cylindrical leading end portion 114 provides the largest diameter of the three portions 114, 116, and 118 (when the implant 100 is in a non-stressed state prior to implantation). In some embodiments, the three portions 114, 116, and 118 are not separately constructed regions, but rather are defined regions of a device constructed from a single piece of mesh material. In other embodiments, the three portions 114, 116, and 118 may be separately constructed and attached together to form the final implant construction. The trailing end portion 118 provides the smallest diameter of the three portions 114, 116, and 118 (when the implant 100 is in a non-stressed state prior to implantation). The transition portion 116 extends between a proximal end periphery of the leading end portion 114 and a distal end periphery of the trailing end portion 118. The transition portion 116 has diameter variance from its distal end portion to its proximal end portion. That is, the transition portion 116 may be tapered (providing either a linear taper or a curved taper), extending proximally from the leading end portion 114 while decreasing in diameter to join with the distal end periphery of the trailing end portion 118. In some embodiments, the transition portion 116 comprises a frustoconical shape. In particular embodiments, some or all of the transitional region 116 has a radiused profile to provide smooth transitions to the leading and trailing portions 114 and 118.

In some embodiments, at least a portion of the leading end portion 114 has a diameter and construction for positioning around a heart in the atrial-ventricular groove AV of the heart H. For example, a hem 113 comprising an elastic band member may be configured for positioning around an atrial-ventricular groove AV (refer to FIG. 1B), to thereby releasably affix the leading end 112 to the heart H. The diameter of the hem 113 (including the elastic band member) may be selected in relation to the size of the heart of a patient. The selected diameter of the hem 113, at rest, will be smaller than the perimeter of the heart at the atrial-ventricular groove, to provide an interference fit therebetween. The high compliance and elasticity of the hem 113 (including the elastic band member) facilitates an interference fit that is effective for maintaining the implant 100 in the targeted position on the heart H while not detrimentally constricting the heart and vessels on the outside of the heart such as the coronary artery or coronary sinus over which the hem 113 may be positioned when the implant 100 is implanted.

Portions of the leading end portion 114, other than the hem 113, are configured for circumferentially encompassing upper portions of the heart ventricles. In addition, some or all of the transition portion 116 may be configured for circumferentially encompassing other portions the heart ventricles. Most or all of the trailing end portion 118 may be configured to extend proximally from the apex of the heart when the leading end 112 is positioned in the atrial-ventricular groove. After installation of the implant 100 on a heart, some or all of the trailing end portion 118 may be trimmed away and removed from the implant 100. Thereafter the trimmed proximal end of the implant 110 may gathered or cinched and closed around the apex of the heart. Closing the proximal open end prevents the implant 100 from migrating toward the superior regions of the heart after implantation. In this manner, the implant 100 can be tailored to fit the patient-specific size and contours of the heart on which the implant 100 is installed.

Multiple sizes of implants 100 are envisioned that are suitable for treating multiple sizes of hearts. For example, the diameters of some or all of portions 114, 116, and 118 can be available in incremental sizes. In some embodiments, the axial lengths of some or all of portions 114, 116, and 118 are also configured in incremental sizes. As will be described further herein, an implant 100 of a particular size can be selected for a patient based on a pre-operative measurement of the patient's heart. For example, in some instances a measurement is taken of the patient's largest ventricular perimeter, and that measurement is used to select the size of implant 100 to be used for that patient. As will be described further herein, various sizes of implants 100, each of which is preloaded on an implant delivery device (refer to FIGS. 5-7), can be available to a clinician, and the clinician can select a particular size of implant 100 based on the measurement of the patient's heart. In some embodiments, a particular size of implant 100 can be used for a range of heart measurement values. For example, a particular size of implant 100 may be used for a range of maximum ventricular perimeters of 36.9 cm to 40.0 cm. Another size of implant 100 may be used for a range of maximum ventricular perimeters of 40.1 cm to 43.4 cm. Still another size of implant 100 may be used for a range of maximum ventricular perimeters of 34.0 cm to 36.8 cm, and so on. It should be understood that these ranges of maximum ventricular perimeters provided are merely illustrative, and are non-limiting examples. In addition, the combination of mesh material compliance and size, hem construction including the compliance of an elastic band on the hem 113, and finable bladder construction include the compliance of materials used to construct together may be selected in accordance with the teachings herein to achieve implant design configurations that enable a fewer number of sizes for a wide range of heart sizes, thereby achieving inventory cost benefits. In some embodiments, the trailing end portion 118 is configured to have the same diameter across all sizes of implants. The fillable bladder 120 may also be implemented with various sizes. For example, larger fillable bladders may be used with larger sized implants, and smaller fillable bladders may be used with smaller sized implants.

Still referring to FIGS. 2A-2C, the leading end 112 in this embodiment is defined by the hem 113. In some embodiments, the hem 113 can be constructed by wrapping some of the mesh material at the distal end of the leading portion 114 around the elastic band, and then securing the free end of the material to an interior portion of the leading end portion 114. Such securing may be continuous or in multiple discreet sections. In particular embodiments an elastic hem band material can be contained within the doubled over layers of mesh material. The elastic hem band material can be made of a low durometer silicon elastomer material, or any other suitable elastic biocompatible material. The diameter of the elastic hem band material, at rest, may be less than the at rest diameter of the mesh material at the hem 113. By way of example, in some embodiments the circumference of the mesh material, at rest, in the hem 113 may be about 25 centimeters, whereas the length of the elastic hem band material may be about 20 centimeters. Such a configuration may accommodate, by way of example only, a heart size wherein the atrial-ventricular groove may be about 30 centimeters in circumference. Owing to the length of the elastic band being longer than the circumference of the mesh material at the hem 113, the mesh material at the hem 113 may be gathered in a slightly wavy or “bunched” configuration about the internal elastic member when the hem 113 is not being stretched around the heart H. In some alternative embodiments, the internal elastic band may not be implemented, and in such cases, the mesh material may be configured into a reduced diameter region in the hem area so as to enable an interference fit of the hem area into an atrial-ventricular groove. In other alternative embodiments, the elastic band serve as the hem 113 and distal end 112 with the mesh material wrapping around it, and in such cases, the mesh material may be bonded to a proximal periphery of the elastic band. Optionally, the trailing end 119 may also be hemmed, and the hem of the trailing end 119 may or may not include an elastic member.

As previously described, some embodiments of the implant 100 include multiple radiopaque markers 115 located around the hem 113 and multiple radiopaque markers 125 located around the periphery of the fillable bladder 120. As described previously, various types of radiopaque markers can be used. In some embodiments, the radiopaque markers 115 and 125 have an adhesive quality during manufacture of the implant 100 that can be used advantageously during the construction of the implant 100. For example, the second group of radiopaque markers 125 can be adhered to the mesh body 110 and, via the interstitial spaces of the mesh, adhered to the fillable bladder 120 to thereby affix the fillable bladder 120 to the implant 100. In one such embodiment, the radiopaque markers 125 (and 115) can be made from raw materials such as a silicone adhesive paste mixed with powdered tantalum. During manufacturing of the implant 100, the mixture can be injected into depressions residing in a metal plate, and that are configured in a generally rectangular pattern as defined by the radiopaque markers 125 shown in the implant 100. The metal plate can thereby act as a mold for forming the radiopaque markers 125. The mesh body 110 can be placed over the metal plate in an orientation that will position the fillable bladder 120 as desired in relation to the mesh body 110. The fillable bladder 120 can be placed on top of the mesh body 110 in an orientation so as to locate the radiopaque markers 125 around the periphery of the fillable bladder 120. A second metal plate can be positioned over the fillable bladder 120. The second metal plate may have a depression that corresponds to the fillable bladder 120. The stacked assembly can then be heated to cure the silicone adhesive paste. In the process, the radiopaque markers 125 become adhered to the mesh body 110 and to the fillable bladder 120. In this manner, the radiopaque markers 125 can be used to affix the fillable bladder 120 to the mesh body 110. Using a similar technique, the radiopaque markers 115 can be formed and adhered to the exterior layer of the mesh material of the hem 113, and adhered to the internal elastic band of the hem 113. Furthermore, the elastic band can thereby be “staked” in relation to mesh material of the hem 113 at the locations of the radiopaque markers 115. In other embodiments, the fillable bladder 120 and/or elastic band of the hem 113 can be affixed to the mesh body 110 using other bonding techniques, such as adhesives, mechanical clips, sutures, interweaving, ultrasonic welding, RF welding, and the like.

Still referring to FIGS. 2A-2C, the implant 100 includes the fillable bladder 120, which as previously described, can be used to exert a localized pressure on a surface of the heart to induce a therapeutic deflection thereto. FIG. 2B illustrates the fillable bladder 120 in a deflated state, and FIG. 2C illustrates the fillable bladder 120 in an inflated state. While the fillable bladder 120 depicted in FIGS. 2A-2C is generally rectangular in shape, other shapes of fillable bladders are also envisioned. For example, fillable bladders can be circular, elliptical, semi-toroidal, triangular, linear, pyramidal, irregularly shaped, and any other like shape, or combinations of shapes.

As previously described, the inflation tube 130 is in fluid communication the fillable bladder 120. The inflation tube 130 is of a flexible tubular construction and is configured to remain in the patient's body as part of the implant 100, and to remain in fluid communication with the fillable bladder 120. The free end of the inflation tube 130 can be positioned subcutaneously, and near to the underside of the epidermis. In some implementations, the free end of the inflation tube 130 is located in an intercostal space after implantation of the mesh body 110 around the heart. So locating the free end of the inflation tube 130 may allow future access to the inflation tube 130 via a simple cut-down procedure through the skin adjacent to the intercostal space between the ribs (e.g., the fifth intercostal space in some implementations). Future inflation or deflation of the fillable bladder 120 may thereby be performed with a minimally invasive access to an intercostal space under the side without extensive surgery to access the pericardium or epicardium.

In some embodiments, the flexible inflation tube 130 is made of silicone, but other biocompatible materials may also be used. In some embodiments, the outer diameter of the inflation tube 130 can range from about 0.065 inches to about 0.25 inches (about 1.60 mm to about 6.40 mm). In one example embodiment, the outer diameter of the inflation tube is about 0.125 inches (about 3.2 mm). In some embodiments, the inner diameter of the inflation tube 130 can range from about 0.031 inches to about 0.125 inches (about 0.78 mm to about 3.18 mm). In one example embodiment wherein the outer diameter of the inflation tube is about 0.125 inches (about 3.2 mm), the inner diameter of the inflation tube is about 0.0625 inches (about 1.58 mm). Such inflation tube dimensions are provided as examples, and it should be understood that other sizes are also envisioned within the scope of this disclosure. In addition, the cross-sectional sizing of the inflation tube may be selected to accommodate the specific inflation material (and in some cases radiopaque contrast agent) that will flow through the tube (discussed below).

The inflation tube 130 provides a flexible conduit through which inflation fluid can be conveyed to inflate or deflate the fillable bladder 120. After inflating or deflating the fillable bladder 120 with a selected volume of inflation fluid, the proximal end region of the inflation tube 130 is sealed to prevent withdrawal of the inflation fluid from the fillable bladder 120. Various types of inflation fluids can be used. For example, the inflation fluid can be a saline liquid solution, silicone gel, gaseous substances, and fluids containing a contrast agent that facilitate visualization of the inflation fluid via imaging systems.

In some embodiments, the fillable bladder 120 is configured of two different sheet components 122 and 124 so that the bladder 120, when inflated, expands more interiorly (that is, toward the heart wall when implanted) than exteriorly. As such, the bladder 120 is configured to provide a differential compliance in which one surface of a bladder 120 is significantly more compliant than the opposing (less compliant) surface of the bladder 120. In the context of fillable bladder 120, the interior sheet component 122 of the fillable bladder 120 is more compliant than the outer sheet component 124 of the fillable bladder 120. When the implant 100 is installed on a heart, the heart is located within the interior region of the mesh body 110 and in contact with the interior sheet component 122 of the fillable bladder 120. The greater compliance of the interior sheet component 122 of the fillable bladder 120 (in relation to the lesser compliance of the outer surface material) can accentuate the localized pressure applied onto the surface of the heart when the fillable bladder 120 is inflated.

Referring now to FIG. 3, some embodiments of the fillable bladder 120 can include the two different layers of sheet components 122 and 124 in the form of an interior sheet component 122 (or inner bladder layer 122) and an outer sheet component 124 (or outer bladder layer 124). A chamber for containing fluids can be formed therebetween by hermetically sealing together the periphery of the sheet components 122 and 124. As discussed above, this sealed periphery of the bladder 120 is the portion of the bladder 120 to which the radiopaque markers 115 are attached through spaces in the mesh material interposed between the bladder 120 and the markers 115. In this embodiment of the bladder 120 shown in FIG. 3, the sheet components 122 and 124 are sealed together using a bonding agent 126, but other techniques are also envisioned, such as ultrasonic welding, solvent bonding, a molded monolithic bladder, and the like. An end portion of the inflation tube 130 is also sealed between the sheet components 122 and 124, such that the lumen of the inflation tube 130 is in fluid communication with the resulting chamber of the fillable bladder 120. In some embodiments, a fitting may be used to couple an inflation tube to a fillable bladder.

The material of the interior sheet component 122 can be selected to have a higher compliance than the material selected for the outer sheet component 124. The interior sheet component 122 can be made of a silicone sheet material, or other biocompatible airtight sheet materials. In some embodiments, the thickness of the interior sheet component 122 is in the range of about 0.005 inches to about 0.050 inches (about 0.12 mm to about 1.30 mm). In one example embodiment, the interior sheet component 122 is a silicone sheet material that is about 0.015 inches (about 0.38 mm) in thickness. The outer sheet component 124 can also be made of a silicone sheet material, or other biocompatible airtight sheet materials. In some embodiments, the material of the outer sheet component 124 can be reinforced (e.g., with a polyester mesh that is impregnated into the sheet) to resist deformation, thereby reducing the compliance of the outer sheet component 124. In some embodiments, the thickness of the outer sheet component 124 is in the range of about 0.005 inches to about 0.070 inches (about 0.12 mm to about 1.78 mm). In one example embodiment wherein the interior sheet component 122 is a silicone sheet material that is about 0.015 inches (about 0.38 mm) in thickness, the outer sheet component 124 is a reinforced silicone sheet material that is about 0.020 inches (about 0.51 mm) in thickness.

Various sizes of inflatable bladders 120 can be constructed, and differently sized inflatable bladders 120 can be used with differently sized implants. In some embodiments, the length and width dimensions of the sheet components 122 and 124 (including the peripheral regions of the membranes that are sealed together) can be in a range from about 0.5 inches to about 4.0 inches (about 12.7 mm to about 101.6 mm). In one example embodiment, the length and width dimensions of the membranes 122 and 124 are in a range from about 1.075 inches to about 2.265 inches (about 27.30 mm to about 57.53 mm). In some embodiments, the fillable bladder 120 has a peripheral seal that is about 0.25 inches (about 6.35 mm) wide, and the sheet material within the peripheral seal is the inflatable portion.

In this embodiment, the peripheral bonding of the sheet components 122 and 124 can be accomplished using the bonding agent 126. The bonding agent 126 can cross-link with the materials of the sheet components 122 and 124 when the bonding agent 126 and sheet components 122 and 124 are heat-soaked as an assembly. In one example, the assembly is heat-soaked at about 350 F (about 177 C) for about 2 hours. Other heat-soaking time and temperature combinations can also be used, and lower temperatures will tend to require longer durations (and vice versa). Various types of bonding agents 126 can be used. In a preferred embodiment, the bonding agent 126 is a non-vulcanized silicone sheet that is about 0.010 inches (about 0.25 mm) thick. After the bonding of the inner and sheet components 122 and 124, and the inflation tube 130, the fillable bladder 120 can be leak tested to confirm that the fillable bladder 120 is hermetically sealed.

Upon implantation and proper positioning of the fillable bladder 120 with respect to targeted heart H structure(s), the fillable bladder 120 (and specifically the bladder's interior sheet component 122) is located and bears against an outer epicardial wall of the heart H, and the mesh material of the mesh body 110 that is located exteriorly of the bladder 120 faces outwardly and bears against the pericardium. When the bladder 120 is inflated, the interior sheet component 122 of the bladder 120 expands inwardly (e.g., expansion from a reference plane defined as extending through the sealed periphery region of the bladder 120) more so than the outer sheet component 124 of the bladder 120 expands outwardly from this reference plane. This characteristic is accentuated in larger bladder embodiments in comparison to smaller bladder embodiments. Therefore, design selections, including interior and outer sheet properties as well as bladder size and other parameters, can be made to attain a fillable bladder with the desired expansion characteristics.

The combination of the implant's mesh body 110 located exteriorly of the bladder 120 (which provides an circumferential restraint force to urge the bladder 120 toward the heart H) and the presence of the pericardium that surrounds the heart H (the pericardium providing a bearing surface against which the implant's mesh material and hence the outer sheet component 124 of the bladder 120 bears) collectively resist outward movement of the bladder 120. This resistance to outward movement of the bladder 120 from the heart H also contributes so that the interior sheet component 122 of the bladder provides localized pressure upon the targeted surface region of the heart. This localized pressure deforms not only the targeted surface region of the heart wall, but also valve structures located inside the chambers of the heart in the location of the localized pressure (refer to FIG. 1B). In addition, at some point in time after implantation (typically in about 1 week to 3 weeks), the mesh body 110 makes a fibrous attachment to both the epicardial wall and to the pericardium. This fibrous attachment of the mesh body 110 to both the epicardial wall and the inner wall of the pericardium increases the resistance to outward movement of the bladder 120, thereby increasing the degree to which the inward expansion of the interior sheet component 122 of the bladder 120 provides localized pressure upon the targeted surface region of the epicardial wall that lies adjacent the bladder 120.

FIGS. 4A and 4B show alternative embodiments having one or more inflatable bladders, as follows. In FIG. 4A, the inflatable bladder is positioned adjacent to the patient's mitral valve. FIG. 4B shows additional placement locations of bladders adjacent to the papillary muscle and tricuspid valve. It is to be understood that the description herein encompasses embodiments with only one or with more than one inflatable bladder. Thus, FIGS. 4A and 4B simply show preferred locations for the bladder placement(s).

As seen in FIGS. 4A-B and 5, the depicted embodiment provides an assembly making up an implant 1 wherein the assembly comprises: a jacket 10 and at least one inflatable bladder 20. Jacket 10 is made of a flexible biocompatible material and has an open top end 12 that is received around the heart H and a bottom portion 14 that is received around the apex A of the heart. In optional aspects, jacket 10 may be made of a knit mesh. This knit mesh may optionally be made of a polymer, including but not limited to high-density polyethylene. Alternatively, jacket 10 may be made of metal.

In one example embodiment, jacket 10 is made of a suitable knit material. An example of such a knit material may be “Atlas Knit” material described above. Alternatively, jacket 10 may be elastic. Optionally, the fibers may be made of Denier polyester. However, other suitable materials, including but not limited to, PTFE, ePTFE, polypropylene and stainless steel may also be used. Advantages of using a knit material include flexibility, fluid permeability and minimizing the amount of heart surface area in direct contact with the jacket (thereby minimizing the potential of scar tissue development).

Inflatable bladder 20 is disposed on an interior surface of jacket 10. Bladder 20 may or may not be attached to jacket 10. FIG. 4B illustrates three separate inflatable bladders 20, one being located near a hem of the implant 1 and being positioned on a posterior portion of the heart H wall adjacent the mitral valve (bladder 20A), one being located away from the hem for positioning to a portion of the heart H wall adjacent to a papillary muscle (bladder 20B), and one being located also near a hem of the implant 1 and positioned on an anterior portion of the heart H wall adjacent the tricuspid valve (bladder 20C). In embodiments wherein the bladder 20 is attached to the jacket 10 prior to implantation of the implant 1, the implant may include one, two or all of the three bladders 20A-C depicted in FIG. 4B. As such, FIG. 4B depicts the different locations where a bladder 20 may be located, wherein some embodiments may include only one or two bladders 20 positioned on the jack 10 so that the bladder 10 may be positioned at the depicted locations shown in FIG. 4B. When bladder 20 (that is, bladder 20A in FIG. 4B) is positioned adjacent to the mitral valve, it is preferably positioned at the P2 area of the valve (in the center of the posterior leaflet) to reduce the distance across the valve, thereby reducing the gap in the valve responsible for the regurgitation. When bladder 20C is positioned adjacent to the tricuspid valve, it performs a similar function, reducing regurgitation through the tricuspid valve. When bladder 20B is positioned adjacent to the papillary muscle, it gently corrects papillary muscle position and relieves tension on the chordae (which otherwise prohibits normal valve functioning).

As seen in FIG. 5, inflatable bladder 20 has an inelastic outer surface 22 positioned adjacent to jacket 10 and an elastic inner surface 24 positioned adjacent to the heart H, as discussed previously in connection with other embodiments. Bladder 20 may optionally be made of silicon. In some embodiments, jacket 10 is relatively non-compliant in comparison to the elastic inner surface 24, the outer surface 22 of bladder 20 positioned adjacent to the bladder is also relatively non-complaint, and the inner surface 24 of bladder 10 is elastic. As a result and as described above, when inflated through fluid supply line 25, inflation of bladder 20 causes the bladder to deform substantially inwardly (i.e.: towards the heart). This then exerts localized pressure against a region of the heart. As can be seen, supply line(s) 25 are positioned inside jacket 10 and extend out of an open bottom end 13 of the jacket adjacent to the apex of the heart. Bottom end 13 may be cinched (and/or sewn) closed after the jacket 10 has been positioned around the heart.

As discussed previously, bladder 20 may be inflated with fluids including air, inert gasses (such as fluorocarbons), silicone gel, saline and contrast agents. Supply lines 25 may optionally be inflated through a blunt needle port, a Luer port fitting, a subcutaneous port 26, etc. In other embodiments, a port-type device may not be used, and instead, the supply lines may be clamped in a closed position, as described previously. Supply lines 25 are made of a suitable bio-compatible material, including but not limited to silicone. This document includes a disclosure of various mechanisms for inflating and deflating bladders 20 post-implementation. For example, in one approach the device is first received onto the heart. After a period of time (e.g.: 30 days) fibrotic encapsulation of mesh jacket 10 will have occurred. At this time, the bladder(s) 20 can then be inflated (through supply line 25 using a needle to percutaneously access filling reservoir 26). Thus, subcutaneous ports 26 may be employed for percutaneous inflation and deflation for therapy optimization or abandonment. Alternatively, and because in some cases implanted subcutaneous port-type devices may have potential drawbacks, clamping of the fluid path tube may be done, with the fluid path staying in the intercostal space and may be accessed by a small “cut-down” procedure to access the tube.

In optional embodiments, jacket 10 has an elastic band 14 passing around its top end 12, as described previously. In addition, radiopaque markers 15 can also be provided around top end 12 of the implant 1.

The present jacket and bladder implant system 1 can be placed around the patient's heart in a variety of different approaches. In an example method of use, the present system further includes a delivery device for positioning the jacket onto the heart, as described later in this document. In one example of the method described later in this document, the assembly is implanted into the patient in a left intercostal mini-thoracotomy using contrast pericardiography and fluoroscopic visualization. After opening the parietal pericardium, the lower portion of the heart is free for applying the jacket over the apex.

In some embodiments, methods of providing localized pressure to a region of a patient's heart H to improve heart functioning may be performed by: (a) positioning an assembly around a patient's heart, wherein the assembly comprises a jacket 10 and at least one inflatable bladder 20, wherein jacket 10 is made of a flexible biocompatible material having an open top end 12 that is received around the heart and a bottom portion 14 that is received around the apex of the heart, and the inflatable bladder 20 is disposed on an interior surface of the jacket, and the inflatable bladder 20 has an inelastic outer surface positioned adjacent to the jacket and an elastic inner surface. In addition, bladder 20 may be inflated causing it to expand such that the bladder deforms substantially inwardly to exert localized pressure against a region of the heart.

In another method of use, a pericardial edge management system (PEMS) may be used in the surgical procedure for safe introduction of the implant 1. A PEMS includes multiple separate sheets that each have one “peel and stick” side, and may be made of Teflon. These sheets can be used to keep the opening into the pericardium open to facilitate insertion of the device without damage to the pericardium (i.e., the insertion tool getting hung up on the edges of the opening). In addition, the PEMS can be used to initially separate the heart from the mesh fabric. After all of the PEMS sheets are pulled out, the jacket fabric can then engage the heart.

Referring to FIGS. 6A-6C, some embodiments of a delivery device 200 can be used by a clinician to install the implant 100 onto a patient's heart. As described in detail below, during a procedure to install the implant 100, some distal portions of the delivery device 100 are temporarily advanced within the body of the patient, while other proximal portions of the delivery device 100 remain external to the patient's body. The delivery device 200 used for installing the implant 100 is a sterile device. In some embodiments, the delivery device 200 is a sterile single-use device. Alternatively, the delivery devices may be designed to be re-sterilized and reused.

In this embodiment, the implant 100 is loaded onto the delivery device 200 at a distal end of the delivery device 200. A main body 210 of the delivery device 200 is located near a proximal end of the delivery device 200. A barrel assembly 220 extends from the main body 210 to the distal end of the delivery device 200. The implant 100 surrounds and is coupled to a distal end of the barrel assembly 220. A proximal end of the barrel assembly 220 is attached to the main body 210. A heart stabilizer assembly 230, which may be configured to releasably anchor to the apex of the hearth H during an implantation procedure, extends from a proximal end of the main body 210 to the distal end of the barrel assembly 220.

In some embodiments, the delivery device 200 and the implant 100 are pre-assembled and packaged together in sterile packaging. That is, the delivery device 200 can be provided to a clinician with the implant 100 pre-loaded onto the delivery device 200 and ready for sterile use. As described elsewhere herein, implants 100 of various sizes are used in order to properly fit multiple sizes of hearts. Therefore, a hospital that performs procedures to install the implants 100 may keep an inventory of various sized implants 100, each of which is pre-loaded on a particular delivery device 200 and packaged in sterile packaging. After the clinician determines the size of patient's heart, the clinician can select from the hospital's inventory the implant 100 that is sized to best fit the patient's heart. The clinician will receive a sterile delivery device 200 that is pre-loaded with that selected size of implant 100. After the implant 100 is deployed from the delivery device 200, the delivery device 200 may be discarded as a single-use instrument (for those embodiments in which the delivery device 200 is packaged as a single-use device).

Still referring to FIGS. 6A-6C, the main body 210 of the delivery device 200 may optionally include a pistol grip type handle 212 for handling by a clinician and also may include a lock release button 214 for the heart stabilizer 230. The pistol grip handle 212 provides a convenient and ergonomic structure by which a clinician can grasp and maneuver the delivery device 200. In some embodiments, the pistol grip handle 212 includes a textured surface to enhance the friction between the pistol grip handle 212 and the clinician's hand. The lock release button 214 in this embodiment is a spring-loaded depressible button that is biased to extend outward from the main body 210. When the lock release button 214 is depressed inward in relation to the main body 210, the heart stabilizer assembly 230 is unlocked and therefore able to translate axially relative to the pistol grip type handle 212. When the lock release button 214 is not depressed, the lock release button 214 extends outward from the main body 210 and the heart stabilizer assembly 230 is locked in its axial position and therefore not able to translate axially.

The barrel assembly 220 of the delivery device 200 may optionally include a splined elongate barrel 222 for guiding the actuators 224 of the delivery device 200. In this embodiment, six actuators 224 are included around the periphery of the barrel 222. In other embodiments, fewer or more than six actuators can be included in a delivery device. The actuators 224 are each individually slidably coupled to a spline of the barrel 222. The actuators 224 are also each individually releasably coupled to an epicardial management strip 250. In this embodiment, there are a total of six epicardial management strips 250. The epicardial management strips 250 extend from the actuators 224, on the external surface of the barrel 222, under the implant 100, and terminate where the implant 100 is coupled to the delivery device 200. The epicardial management strips 250 provide low-friction surface area that facilitates the advancement of the implant 100 onto a heart. The epicardial management strips 250 are not shown in FIG. 6C so that other components of the implant 100 and delivery device 200 are visible.

Still referring to FIGS. 6A-6C, the heart stabilizer assembly 230 can include a vacuum connection fitting 232, a shaft rack 234, a vacuum tube 236, and a distal vacuum cup 238. Those components of the heart stabilizer assembly 230 are affixed together in the configuration as shown. That is, when the heart stabilizer assembly 230 is moved in relation to the other parts of the delivery device 200 (while the lock release button 214 is depressed), the vacuum connection fitting 232, heart stabilizer shaft rack 234, vacuum tube 236, and vacuum cup 238 move as a unit together in the axial direction.

In this embodiment, the vacuum connection fitting 232 is a barbed fitting. Other types of fittings can also be used, such as luer connections, compressing fittings, threaded fittings, quick-lock fittings, and the like. A source of negative pressure (vacuum) can be connected via flexible tubing (not shown) to the vacuum connection fitting 232. The negative pressure will be communicated from the vacuum connection fitting 232, through the vacuum tube 236, and to the vacuum cup 238.

The shaft rack 234 of the heart stabilizer assembly 230 is configured to be releasably engageable with the lock release button 214. Engagement between the shaft rack 234 and the lock release button 214 effectuates the locking of the heart stabilizer assembly 230 in a selected axial position in relation to the main body 210 and barrel assembly 220. Disengagement of the shaft rack 234 and the lock release button 214 (when the lock release button 214 is depressed) unlocks the heart stabilizer assembly 230 such that the heart stabilizer assembly 230 can move axially in relation to the main body 210 and barrel assembly 220.

In this embodiment, the shaft rack 234 includes a series of holes with which one or more protrusions on the shaft lock release button 214 engage. When the lock release button 214 is extending outward from the main body 214 (which is the default position of the button 214), the one or more protrusions on the lock release button 214 extend into one or more holes on the shaft rack 234 to lock the heart stabilizer assembly 230 in place. In contrast, when the lock release button 214 is depressed towards the main body 214 (e.g., by manually pushing the button 214), the one or more protrusions on the lock release button 214 become disengaged from the holes on the shaft rack 234. As a result of depressing and maintaining the lock release button 214 in a depressed position, the heart stabilizer assembly 230 becomes unlocked and free to move axially in relation to the other parts of the delivery device 200. That is the case because depressing and maintaining the lock release button 214 in a depressed position disengages the protrusions of the lock release button 214 from the holes of the shaft rack 234. When the lock release button 214 is no longer maintained in the depressed position, the outward bias of the lock release button 214 causes the button 214 to translate to an extended position to once again lock the heart stabilizer assembly 230 in relation to the other parts of the delivery device 200.

In one example, a comparison of FIGS. 6A and 6B illustrates how the heart stabilizer assembly 230 can translate axially when the lock release button 214 is pressed. For example, in FIG. 6A the heart stabilizer assembly 230 is in an axially retracted position (a proximal position). To extend the heart stabilizer assembly 230 distally (e.g., to the position shown in FIG. 6B), first the lock release button 214 is manually pressed and maintained in a depressed position, and then the heart stabilizer assembly 230 can be manually slid distally in the axial direction. In the configuration of FIG. 6B, and as will be described further below, the vacuum cup 238 extends distal-most and is positioned to be the initial member of the delivery device 200 to be inserted into the chest cavity of a patient during an implant 100 installation procedure.

Various other design embodiments for locking and unlocking the heart stabilizers are also envisioned. Such embodiments can include the use of, but are not limited to, eccentric collars, cam mechanisms, interlocking tapers, over-center devices, set screws, and the like.

Still referring to FIGS. 6A-6C, the location of the fillable bladder 120 on the implant 100, and more specifically, the relative orientation of the fillable bladder 120 in relation to the pistol grip handle 212 of the delivery device 200 can provide a number of benefits in some embodiments. For example, the implant 100 can be loaded onto the delivery device 200 in a predetermined orientation such that the location of the fillable bladder 120 in relation to the pistol grip handle 212 facilitates alignment of the bladder with a targeted surface region of the heart H during deployed of the implant 100 over the heat H. In such circumstances, a clinician may be able to ascertain the position of the fillable bladder 120 based on the position of the pistol grip handle 212. This feature can be advantageous, for example, during an implantation procedure when the fillable bladder 120 is within the chest cavity of a patient and therefore out of the direct sight of the clinician. For example, during use, the clinician will be estimate the location of the fillable bladder 120 relative to the targeted surface region of the heart based on the orientation of the pistol grip handle 212 in the clinician's hand.

In this embodiment illustrated in FIG. 6C, when viewing on an axial sight-line in a proximal direction at the distal end of the delivery device 200, the fillable bladder 120 is on the left side of the delivery device 200 (e.g., at the “9 o'clock” position) when the pistol grip handle 212 is extending vertically downward (e.g., at the “6 o'clock” position). Stated in another way, and as shown in the side views of FIGS. 6A and 6B, from the perspective of a clinician holding the pistol grip handle 212 vertically downward and in front of the clinician (e.g., see FIG. 16A), the fillable bladder 120 is located on the right side of the delivery device 200 (e.g., at the “3 o'clock” position relative to the “6 o'clock” position of the handle 212). Other embodiments may use different variations of orienting a fillable bladder in relation to the delivery device. For example, in some embodiments the fillable bladder may be located on the other side of the delivery device, on the upper or lower sides, or at any other position around the periphery of the barrel assembly 220.

Referring now to FIG. 7 (in addition to FIGS. 6A and 6B), some embodiments of the delivery device 200 include multiple epicardial management strips 250 that are positioned between the barrel 222 and the implant 100 during advancement of the implant 100 toward and over the apex of the heart H. As mentioned previously, epicardial management strips 250 can be used to assist with the installation of an implant 100 onto the heart H. As the implant 100 is slid over the heart H, the epicardial management strips 250 can be temporarily positioned between the epicardial surface of the heart and the implant 100. The epicardial management strips 250 can be made of a flexible, lubricious material to provide low-friction surface area that facilitates the sliding advancement of the implant 100 onto the heart. In this embodiment, the epicardial management strips 250 are components of the delivery device 200 and are preloaded on the delivery device 200, as is the implant 100. After the implant 100 is installed and seated in the selected position (e.g., with the hem 113 positioned in the atrial-ventricular groove of the heart H), the epicardial management strips 250 are removed from the chest cavity.

The epicardial management strips 250 can be made from a variety of different materials, including but not limited to, polytetrafluoroethylene (PTFE), expanded-PTFE (ePTFE), ultra-high-molecular-weight polyethylene (UHMWPE), fluorinated ethylene propylene (FEP), perfluoroalkoxy (PFA), and the like. In some embodiments, a lubricious coating or surface treatment can be applied to the material used to make the epicardial management strips 250. The materials selected to construct the epicardial management strips 250 have properties such as a low coefficient of friction, biocompatibility, and resistance to absorption of liquids. The thickness of the epicardial management strips 250 can be selected to provide the desired levels of lateral flexibility, column strength, and other mechanical properties. For example, in some embodiments the thickness of the epicardial management strips 250 are in the range of about 0.010 inches to about 0.100 inches (about 0.25 mm to about 2.54 mm).

In this embodiment, there are a total of six epicardial management strips 250. The epicardial management strips 250 extend from the actuators 224, over the external surface of the barrel 222, under the implant 100, and terminate where the implant 100 is coupled to the delivery device 200. In this embodiment, the epicardial management strips 250 include a proximal portion 252, a distal portion 254, and an intermediate portion 256 therebetween. The proximal portion 252 includes a first clearance hole 253 that is configured to engage with a barbed protrusion located on the actuators 224. The distal portion 254 is a widened area that slides on the heart's surface as an implant 100 is being installed. A second clearance hole 255 is located at the distal portion 254. The second clearance hole 255 is configured to allow a portion of the mesh material of the implant 100 to pass therethrough, whereafter the portion of mesh material is releasably coupled with the delivery device 200.

Referring now to FIGS. 8A-8E, the delivery device 200 is illustrated from multiple perspectives. In these views, the implant 100 and epicardial management strips 250 are not shown for purposes of illustrating the barrel assembly 220 and other components distal thereto. As described previously, the delivery device 200 includes the main body 210, barrel assembly 220, and heart stabilizer assembly 230. In addition, the delivery device 200 includes multiple elongate arm assemblies 240. As described further herein, the arm assemblies 240 can be individually and selectively extended from the barrel assembly 220 to convey the implant 100 onto a heart. Thereafter, the arm assemblies 240 can be decoupled from the implant 100 and retracted from the patient's chest space (along with the epicardial management strips 250 not shown in FIGS. 8A-8E), while the implant 100 remains in a selected position on the patient's heart H (e.g., with the hem 113 positioned in the atrial-ventricular groove of the heart H).

The arm assemblies 240 extend from the distal end of the barrel assembly 220 and terminate at free ends 244. A proximal end of each arm assembly 240 is coupled to an actuator 224. In this embodiment, the delivery device 200 includes six actuators 224 and six corresponding arm assemblies 240. Other embodiments may include more than six or fewer than six actuators and arm assemblies. In this embodiment, each actuator 224 is coupled to one and only one arm assembly 240, and each arm assembly 240 is coupled to one and only one actuator 224. However, in some embodiments, more than one arm assembly may be coupled to one actuator. As described further herein, the distal free ends 244 of the arm assemblies 240 are configured to releasably couple with the mesh material of an implant (refer, for example, to FIG. 6C).

Referring to FIGS. 8F and 8G, the elongate arm assemblies 240 are laterally flexible and axially extendable members. That is, each of the arm assemblies 240 can elastically bend laterally and translate axially in the depicted embodiment. Such properties can be useful for conveying an implant through a relatively small chest opening, into the pericardial cavity of a patient, and then onto the ventricles of the patient's heart H in an atraumatic manner.

In this embodiment of the delivery device 200, the elongate arm assemblies 240 can be manually adjusted between a retracted position (depicted in FIG. 8F) and an extended position (depicted in FIG. 8G). In the extended position, the elongate arm assemblies 240 project distally from the distal end 221 of the barrel assembly 220 to a greater extent than when the arm assemblies 240 are in the retracted position. This ability of the arm assemblies 240 to extend distally is useful for the purpose of conveying an implant onto the heart of a patient. That is, while the distal end 221 of the barrel assembly 220 remains outside of the chest cavity, the arm assemblies 240 can be extended through a chest incision, and then extended into the chest cavity of the patient. The arm assemblies 240 can be extended further to project around the ventricles of the patient's heart to place the implant 100 onto the heart H (e.g., refer to FIGS. 1B, 4A, and 4B). The flexibility of the arm assemblies 240 can be useful because the arm assemblies sustain flexure during the minimally invasive implantation procedure. For example, after passing through the chest incision, at least some of the arm assemblies 240 thereafter bend to follow the contours of the heart H. Because the arm assemblies 240 are laterally compliant, the arm assemblies 240 can enter the chest through a small incision (e.g., a mini-thoracotomy) and elastically flex within the chest cavity to convey an implant 100 onto the patient's heart H.

In the depicted embodiment, the arm assemblies 240 can be extended and retracted by moving the arm actuators 224. That is the case, because the proximal ends of the arm assemblies 240 are coupled to the actuators 224. In order to axially move an arm assembly 240, the corresponding actuator 224 can be slid along the splined elongate barrel 222. For example, because the actuators 224 are located near the proximal end of the splined elongate barrel 222 in FIG. 8F, the arm assemblies 240 are in retracted positions. In contrast, because the actuators 224 are located near the distal end of the splined elongate barrel 222 in FIG. 8G, the arm assemblies 240 are in extended positions.

Referring to FIGS. 9A-9C, the arm actuators 224, and the corresponding arm assemblies 240 coupled thereto, can be individually axially translated along the axis of the splined elongate barrel 222. For example, arm actuator 214 a has been slid to a location that is distal of the other arm actuators 224. The corresponding arm assembly 240 a is therefore extended further distally from the distal end 221 of the barrel 222 than the other arm assemblies 240. In some embodiments, multiple arm actuators 224 and arm assemblies 240 can be moved concurrently using a mechanical member that simultaneously translates the multiple arm actuators 224.

In this embodiment of the delivery device 200, the actuators 224 and the arm assemblies 240 are each individually slidably coupled with a spline 223 of the barrel 222. Each arm assembly 240 can be at least partially disposed in a corresponding spline 223 of the splined elongate barrel 222. For example, arm assembly 240 a is partially disposed in spline 223 a. The open space defined by the splines 223 is larger than the outer profile of the portion of the arm assemblies 240 disposed therein. As such, the arm assemblies 240 are free to slide axially within the splines 223. The arm actuators 224 are also partially disposed in or engaged with a particular spline 223. For example, arm actuator 224 a is engaged with spline 223 a. The arm actuators 224 include shuttle portions that have shapes that are complementary to the shape of the splines 223. As a result, the arm actuators 224 are coupled to, and are slidable in relation to, the splines 223.

Referring to FIGS. 9A-9C and FIG. 10, the main body 210 can include an actuator lock ring 216. The actuator lock ring 216 can be operated to retain the arm actuators 224 at the arm actuator's 224 proximal-most position on the barrel 222. This feature can be useful for purposes of restraining the arm assemblies 240 from inadvertently extending.

The actuator lock ring 216 can be rotatably coupled to the main body 210. That is, in this embodiment the actuator lock ring 216 is coupled to, and is free to be manually rotated in relation to the main body 210. In addition, the actuator lock ring 216 can be manually rotated in relation to the barrel 222 and the arm actuators 224 slidably coupled thereto.

The actuator lock ring 216 includes a rotatable lock knob 218 that can be manually rotated to lock or unlock the actuators 224 to the main body 210. The actuator lock ring 216 also includes six slots 217 (shown in FIG. 10) that are disposed about the inner diameter of the ring 216. The slots 217 are configured to be selectively alignable with the splines 223 of the barrel 222. The slots 217 are also configured to receive actuator tabs 225 (refer to FIG. 9C) that are located on the proximal ends of the arm actuators 224. When the slots 217 of the actuator lock ring 216 are in alignment with the splines 223, and the arm actuators 224 are slid to the distal-most end of travel on the barrel 222, then the tabs 225 pass through the slots 217 and reside proximally to the slots 217. Thereafter, the actuator lock ring 216 can be rotated via the lock knob 218 such that the slots 217 are no longer aligned with the splines 223, thereby locking the arm actuators 224 to the main body 210. For example, in FIG. 9A the actuator lock ring 216 is in a rotary position where the slots 217 are not aligned with the splines 223. Therefore, the arm actuators 224, other than actuator 224 a, are locked to the main body 210. In contrast, in FIG. 9B the actuator lock ring 216 is in a rotary position where the slots 217 are aligned with the splines 223. For instance, slot 217 a is visibly aligned with slot 223 a. Therefore, all of the arm actuators 224 are not locked to the main body 210. In result, the arm actuators 224 can be slid in relation to the main body 210 and splined barrel 222.

In the cross-sectional view of FIG. 9B, it can be seen that each of the arm assemblies 240 include an elongate hollow outer jacket 241. The hollow outer jacket 241 defines an open interior space, or lumen, that can contain another member, such as a core member 242 described in connection with FIGS. 11A-11B.

Referring now to FIGS. 11A and 11B, in this embodiment each of the arm assemblies 240 include the hollow outer jacket 241, the core member 242, and an arm cap 243. The core member 242 is slidably disposed within the lumen of the hollow outer jacket 241. The arm cap 243 is affixed to the distal end of the hollow outer jacket 241. Therefore, the core member 242 can also be slid in relation to the arm cap 243. In other embodiments, other configurations of the arm assemblies 240 can be used while providing similar functionality.

As described previously, arm actuators 224 are coupled to corresponding arm assemblies 240. For example, when an arm actuator 224 is axially translated in relation to the splined barrel 222, a corresponding arm assembly 240 is extended or retracted from the distal end 221 of the barrel 222. As each arm assembly 240 is extended or refracted, the hollow outer jacket 241, core member 242, and arm cap 243 of the arm assembly 240 can be extended or retracted in equal distances, and in unison.

The arm actuators 224 are coupled to arm assemblies 240 in a second manner that allows each actuator 224 to move the core members 242 of the corresponding arm assembly 240 relative to the hollow outer jacket 241 and arm cap 243. In particular, the arm actuators 224 are coupled to the core members 242 such that pivoting an actuator lever 226 of an arm actuator 224 can advance or retract a core member 242 of an arm assembly 240 in relation to the outer jacket 241 and arm end 243 of the arm assembly 240. The pivotable actuator lever 226 of an actuator 224 controls the core member 242 of the arm assembly 240 to which the actuator 224 is coupled.

The pivotable actuator lever 226 is shown pivoted away from the barrel 222 in FIG. 11A, such that the longitudinal axis of the pivotable actuator lever 226 is roughly perpendicular to the axis of the barrel 222. In contrast, the pivotable actuator lever 226 is shown pivoted toward the barrel 222 in FIG. 11B, such that the longitudinal axis of the pivotable actuator lever 226 is roughly parallel with the axis of the barrel 222. Such pivoting of the actuator lever 226 controls the axial position of the core member 242 in relation to the hollow outer jacket 241 and the arm cap 243. For example, in FIG. 11A no core member is visible within the window of the arm cap 243. In contrast, in FIG. 11B, the core member 242 is visible within the window of the arm cap 243. This comparison illustrates that, in this embodiment, when an actuator lever 226 is pivoted away from the barrel 222, a core member 242 is retracted in the axial direction. Conversely, when an actuator lever 226 is pivoted toward the barrel 222, a core member 242 is advanced distally in the axial direction.

This second manner by which arm actuators 224 are coupled to arm assemblies 240 can be operated independently of axially translating an arm actuator 224 in relation to the splined barrel 222 to extend or retract a corresponding arm assembly 240. So, for example, at any axial position of an arm actuator 224, the actuator lever 226 can be pivoted to advance or retract the core member 242. Further, the two movements (axial translation of an arm actuator 224 and pivoting of the actuator lever 226) can be performed contemporaneously.

The advancing and retracting of the core members 242 within the windows of the arm ends 243 can be advantageously used for releasably coupling an implant to the delivery device 200. In some embodiments, a portion of the mesh body 110 of the implant 100 can be crimped and contained within a window of an arm end 243 (refer, for example, to FIG. 6C) when the core member 242 is in the advanced position. When it is desired to release the implant 100 from the delivery device 200, the actuator levers 226 can be pivoted to retract the core members 242, and the mesh material will then no longer be crimped within the windows of the arm ends 243, and the implant 100 can then be separated from the delivery device 200. Thereafter, the arm assemblies 240 can be retracted from the patient's chest space (along with the epicardial management strips 250 not shown in FIGS. 8A-11B), while the implant 100 remains in a selected position on the patient's heart H (e.g., with the hem 113 positioned in the atrial-ventricular groove of the heart H).

Referring now to FIGS. 12A-12C, some embodiments described herein include a method 300 for installing an implant in a patient to treat a heart condition. In some implementations, such heart conditions can include, but are not limited to, functional mitral regurgitation, tricuspid valve regurgitation, and congestive heart failure. In some embodiments of the method 300, a cardiac implant (including but not limited to the implant 100 described above) is implanted to surround an exterior portion of the patient's heart. The implant employed in the method 300 may include one or more fillable bladders. The fillable bladders can be configured for installation at a selected position on the targeted epicardial region of the heart (for example, on a posterior wall of the heart adjacent the mitral valve) so that the fillable bladder will exert a localized pressure to induce the remodeling of a portion of the heart when the fillable bladder is inflated. In the example of positioning a fillable bladder on a posterior wall of the heart adjacent the mitral valve, the fillable bladder provides localized pressure that in turn is applied to a posterior portion of the mitral valve annulus (refer to FIG. 1B), thus bringing the leaflets of the valve into closer proximity with one another and treating a mitral valve regurgitation problem.

Referring to FIG. 12A, in some implementations of the method 300, step 302 includes identifying the apex of a patient's heart. This step may involve the use of one or more imagining modalities. For example, in some embodiments, radiographic and/or transthoracic echocardiographic information is attained to assist in the identification of the apex of the heart.

At step 304 in some implementations of the method 300, a location for an incision to access the patient's heart is selected, and then an incision through the patient's skin is made. In some embodiments, the selected location of the incision will allow access to the apex of the heart in alignment with the long axis of the heart. Such an incision can allow an implant delivery device to be inserted into the patient's chest cavity substantially coaxially with the heart (e.g., as in step 326). Therefore, the location for the incision can be made at least partly based on the location of the apex of the patient's heart as ascertained in step 302. In some implementations, an intercostal incision location is selected. For example, in particular implementations the fifth intercostal space may be selected. However, the selected incision location can be patient-specific. In some implementations, the incision comprises a mini-thoracotomy heart access procedure. In some embodiments of method 300, a minimum size of incision is recommended. For example, for the delivery device 200 described above, a minimum incision of 7 cm is recommended, although that is optional in some implementations.

At step 306 in some implementations of the method 300, surgical retraction is performed to create and maintain a surgical passageway through the patient's incised skin. In some implementations, a low-profile retractor is used. In some embodiments of method 300, a separation distance of the retractor blades is recommended. For example, when the delivery device 200 described above will be used, the retractor blades should be separated by at least about 4 cm.

At step 308 in some implementations of the method 300, the pericardium is incised and retracted to provide access to the heart's apex. In some embodiments, the selected location of the incision will allow access to the apex of the heart in alignment with the long axis of the heart. In some embodiments of method 300, a minimum size of incision is recommended. For example, for the delivery device 200 described above, a minimum incision of 7 cm is recommended, although that is optional. The edges of the pericardium can be retracted by suturing the edges to the surrounding tissues.

At step 310 in some implementations of the method 300, an inspection is made for pericardial adhesions. Pericardial adhesions are an attachment of the pericardium to the heart muscle. In some implementations, contrast agent solution may be injected into the pericardium to enhance visualization of pericardial adhesions. If pericardial adhesions that may impede complete circumferential access to the heart are identified, the clinician may abandon the method 300 at this point.

At step 312 in some implementations of the method 300, multiple pericardial edge management strips (PEMS) are installed. The PEMS can be used to cover exposed edges of the pericardium, and to create a clear tunnel for access (e.g., by delivery tool 200) to the apex of the heart. In some implementations, four to six PEMS are installed. In other implementations, fewer than four or more than six PEMS may be installed. The PEMS are sterile devices.

One example embodiment of PEMS is illustrated in FIGS. 13A and 13B. As shown, in some embodiments the PEMS 400 includes a masking member 410, a malleable member 420, and an adhesive member 430. The malleable member 420 and the adhesive member 430 can be attached to the masking member 410. In some embodiments, the malleable member 420 is disposed between multiple layers of masking member 410 material. The masking member 410 can be a flexible biocompatible film such as Teflon, polyester, polyurethane, and the like. The malleable member 420 can be a thin gauge metallic material, such as a stainless steel, titanium, and the like, or alloys thereof. The adhesive member 430 can be a pressure-sensitive biocompatible material such as a medical-grade acrylic adhesive, or other medical-grade adhesives. The adhesive member 430 can comprise an adhesive pad or be coated onto the masking member 410. The adhesive member 430 is covered by a liner 432 that is removed when the PEMS 400 are put into use.

One non-limiting example of step 312 (using the PEMS 400) is illustrated in FIG. 13C. A retractor device 440 for spreading open an incision in the chest 460 of a patient depicted. Four PEMS 400 are partially inserted in the chest cavity of a patient to create an access tunnel 450. The end opposite the adhesive member 430 is inserted through the incision and into the pericardial space. Care is used to ensure that the inserted end of the PEMS 400 is within the pericardial space and is not inserted too deep into the incision such that the PEMS 400 will interfere or damage other cardiac structures. The exposed portion of the PEMS 400 is bent back (thereby deforming the malleable member 420) so that the PEMS 400 is in contact with the sterile surgical drape around the incision site. The adhesive liner 432 is removed. The adhesive member 430 of the PEMS 400 is adhered to the sterile surgical draping on the chest 460 of the patient. This process is repeated with additional PEMS 400 until the all edges of the pericardium are covered by PEMS 400.

Referring again to FIG. 12A, in some implementations of the method 300, step 314 includes identifying the atrial-ventricular groove. In some implementations, the atrial-ventricular groove is identified using fluoroscopy. Multiple fluoroscopic images from various angles may need to be used to ascertain the location of the atrial-ventricular groove. In some implementations, the injection of a contrast solution into the pericardial space (e.g., between the pericardium and the epicardium) may enhance the visibility of the atrial-ventricular groove. The boundaries of other cardiac structures may also be determined in this step.

In some implementations of the method 300, the optional step 316 includes intra-operatively measuring the ventricular perimeter of the patient's heart. In some instances, the measurement may have already been performed pre-operatively using imaging modalities such as a CAT scan, MRI, ultrasound, and the like. In such instances, step 316 may be optional to perform.

An example intra-operative sizing device 500 for performing step 316 is depicted in FIGS. 14A-14C. In some embodiments, the sizing device 500 includes a main body 510, a vacuum assembly 520, sizing arms 530, and sizing cords 540. The vacuum assembly 520 is slidable in relation to the main body 510. The arms 530 are fixed to the main body 510. The cords 540 (in the embodiment depicted there are three cords) are attached at one end to the end cap 532 of one of the arms 530, and at another end to a sizing positioner 512 in the main body 510.

In some embodiments, the main body 510 includes a casing 511, sizing positioners 512, a sizing indicator 513, and a sizing scale 514. The sizing positioners 512, which are linked to the sizing indicator 513, are slidable in relation to the casing 511. The sizing scale 514 is affixed to the casing. As the sizing positioners 512 are axially translated, the sizing indicator 513 moves in unison. The clinician can ascertain the measurement by viewing the sizing indicator 513 in relation to the sizing scale 514.

The sizing device 500 also includes a vacuum assembly 520. In some embodiments, the vacuum assembly 520 can include a vacuum fitting 521, a knob 522, a vacuum shaft 523, and a vacuum stabilizer cup 524. The aforementioned components of the vacuum assembly 520 are affixed to each other and axially translate in relation to the main body 510 as a unit. The vacuum fitting 52 is in fluid communication with the vacuum shaft 523, which is in fluid communication with the vacuum stabilizer cup 524. Hence, when a source of negative pressure is attached to the vacuum fitting, negative pressure is communicated to the vacuum shaft 523 and vacuum stabilizer cup 524.

In some embodiments, the sizing device 500 also includes multiple sizing arms 530. In the depicted embodiment, three arms 530 are included that are disposed at about 120 degrees apart from each other. In other embodiments, fewer or more arms are included. One end of the arms are affixed to the main body 510, while the other ends of the arms 530 are free ends having end caps 532. The arms 530 are laterally elastically flexible. That is, the arms 530 can radially deflect away from the vacuum shaft 523 while having one end affixed to the main body 510. As such, in some embodiments the arms 530 are made from a polymeric material such as Acrylonitrile Butadiene Styrene (ABS), Polyvinyl Chloride (PVC), Cellulose Acetate Butyrate (CAB), Polyethylene (PE), High Density Polyethylene (HDPE), Low Density Polyethylene (LDPE or LLDPE), Polypropylene (PP), Polymethylpentene (PMP), Polycarbonate (PC), Polyphenelyne Ether (PPE), Polyamide (PA or Nylon), and the like. The end caps 532 include clearance holes through which a sizing cord 540 freely passes.

The sizing device 500 also includes sizing cords 540. In the embodiment depicted, three sizing cords 540 are included. In other embodiments, fewer or more cords are included. The cords can be comprised of a biocompatible material such as, but not limited to, PTFE, ePTFE, polypropylene, polyglycolide, nylon, and other like materials. Each cord 540 have two ends. A first end of the cords 540 is attached to the sizing positioners 512, and a second end of the cords are individually attached to an end cap 532. Therebetween, the cords 540 individually pass through a clearance hole in an end cap 532.

In one embodiment, the process for using the sizing device 500 is as follows. A source of negative pressure is connected to the vacuum fitting 521. The vacuum assembly 520 is fully extended in relation to the main body 510. The vacuum stabilizer cup 524 is inserted through the chest incision and placed in contact with the apex of the heart. The main body 510, and sizing arms 530 affixed thereto, are carefully advanced into the pericardial cavity so that the arms 530 and the cords 540 surround the heart. An imaging system, such as a fluoroscope, can be used to provide visualization of the advancement. As the arms and cords 540 are advanced, the sizing positioners 512 may move distally in relation to the main body 510 as the cords 540 require additional length to surround the heart. The advancement is stopped when the sizer cords 540 are around the largest perimeter of the heart. The sizer positioners 512 are then carefully pulled back (manually) to remove any slack in the cords 540. Using fluoroscopy, the clinician confirms that the cords 540 are not over-tightened (e.g., that the heart is not indented by the cords 540). The clinician then observes the relative position of the sizing indicator 513 to the sizing scale 514. The clinician can thereby ascertain the size of the largest perimeter of the heart, and thereafter remove the sizing device 500.

Referring again to FIG. 12A, in some implementations of the method 300, step 318 can include selecting an implant, which may be include selecting the implant based at least in part on the size of the patient's heart as determined previously. In some embodiments, the implant will be pre-loaded on a delivery device in sterile packaging, as previously described herein. The epicardial management strips may also be pre-loaded on the delivery device.

At step 320 in some implementations of the method 300, a source of negative pressure is connected to the delivery device. In the context of the example delivery device 200, the negative pressure is attached to vacuum connection fitting 232. The negative pressure will be communicated to the vacuum cup 238 of the heart stabilizer 230.

At step 322 in some implementations of the method 300, the vacuum stabilizer is fully extended. In the context of the example delivery device 200, the heart stabilizer 230 is fully extended in relation to the main body 210.

At step 324 in some implementations of the method 300, the vacuum stabilizer is inserted through the incision and into pericardial tunnel. An example of this step is illustrated in FIG. 15. There the vacuum cup 238 of example delivery device 200 is being inserted into the pericardial tunnel 450. The implant 100 is coupled to the delivery device 200.

Referring now to FIG. 12B, at step 326 the fillable bladder is rotationally aligned to a target location on the heart, in accordance with some implementations of the method 300. For example, in some instances the target location may be on the posterior lateral surface of the heart where the fillable bladder will be able to deflect the “P2” portion of the posterior leaflet of the mitral valve to treat FMR. Other target locations may be selected in other instances depending on the condition to be treated using method 300. In this step, the relative positioning between features of the delivery device and the fillable bladder can be used advantageously. In the context of the example delivery device 200, as explained above, the relative orientation of the fillable bladder 120 in relation to the pistol grip handle 212 of the delivery device 200 can have a predetermined orientation such that a clinician may be able to ascertain the position of the fillable bladder 120 based on the conveniently held position of the pistol grip handle 212 over the patient's body. Based on the known orientation, the clinician will be estimate the location of the fillable bladder 120 relative to the targeted surface region of the heart based on the orientation of the pistol grip handle 212 in the clinician's hand.

At step 328 in some implementations of the method 300, the vacuum stabilizer is applied to the apex of the patient's heart. The negative pressure at the delivery device is active at this step. Therefore, the vacuum stabilizer becomes attached to the apex using vacuum. The apex of the heart is thereby stabilized in relation to the delivery device.

At step 330, the arm actuators can be unlocked. In the context of the example delivery device 200, the clinician rotates the actuator lock ring 216, as previously described. Thereafter, all of the arm actuators 224 are not locked to the main body 210, and the arm actuators 224 can be slid in relation to the main body 210 and splined barrel 222 of the delivery device 200.

At optional step 332 in some implementations of the method 300, the heart can be temporarily elongated. The clinician can perform this step by exerting a slight directed pull on the delivery device in a proximal direction. Doing so may elongate the shape of the heart at the heart's apex and ease the initial deployment of the delivery tool's arms over the heart.

At step 334, the arms of the delivery device are incrementally extended while using imaging to view the position of the arms relative to the heart. FIGS. 16A-16C illustrate one non-limiting example of the step 334, in accordance with some implementations of the method 300. In FIG. 16A a clinician is shown operating a delivery device 200. The clinician is extending the arms 240 of the delivery device, incrementally and individually, by sliding the actuators 224 distally. Contemporaneously, the clinician is observing the video screen of an imaging system 600 (refer to FIG. 16B) whereby the clinician can view the positions of the arms 240 in relation to the heart H. In some implementations, the radiopaque markers of the implant 100 (described above) may also aid in the contemporaneous visualization process and to verify the positioning of the hem 113 and the bladder 120 relative to particular landmarks of the heart H. FIG. 16C illustrates an implant 100 that is coupled to arms 240 as the arms are being extended so as to position the implant 100 around the ventricles of the heart H. The arms 240 are advanced carefully, and in many circumstances, no single arm 240 is greatly advanced further than the others. For example, in some implementations it is recommended that no single arm 240 be positioned more than about 2 cm beyond any other arm 240. In some implementations, it may be advantageous to modulate the extension distance of the vacuum stabilizer in relation to the rest of the delivery device so as to achieve a desirable balance between flexibility and column strength of the arms during this step.

At step 336, the arms are further advanced to position the leading hem of the implant in the atrial-ventricular groove of the heart. This positioning of the implant in the atrial-ventricular groove is depicted in FIG. 1B, for example. As previously described herein, radiopaque markers may be mounted on the implant to assist with the contemporaneous visualization process and to verify the positioning of the hem 113 and the bladder 120 relative to particular landmarks of the heart H. In the context of the example delivery device 200, one or more radiopaque markers 115 located on the hem 113 and one or more radiopaque markers 125 of the bladder 120 can be used as reference points in conjunction with an imaging system.

At step 338, the delivery device is decoupled from the implant. In the context of the example delivery device 200, pivoting an actuator lever 226 of an arm actuator 224 can retract a core member 242 of an arm assembly 240 in relation to the outer jacket 241 and arm end 243 of the arm assembly 240 to decouple the arm assembly 240 from the implant 100. This process can be repeated for every arm assembly 240 to fully decouple the implant 100 from the delivery device 200.

At step 340 the arms of the delivery device can be retracted. For instance, using the delivery device 200 as an example, the arm actuators 224 can be slid proximally to withdraw each arm assembly while leaving the implant 100 on the heart H. The epicardial management strips 250 are also retracted along with the arms 240.

At step 342, the delivery device is withdrawn from the patient. The negative pressure source is discontinued, and then the entire delivery device is withdrawn. One non-limiting example of this step is illustrated in FIG. 17.

Referring again to FIG. 12B, at step 344 the fillable bladder(s) are inflated while patient parameters are monitored. Sterile saline solution or other types of inflation fluids may be used to inflate fillable bladders. For example, the inflation fluid can be dispensed from a syringe device or other inflation delivery device that is temporarily coupled to the proximal end opening of the tube. When the condition being treated is valvular regurgitation, the valve may be monitored using, for example, transesophegeal echocardiography or other like techniques, while the inflation is taking place. Such contemporaneous monitoring may assist the clinician to determine the volume of inflation fluid to administer into the fillable bladder(s). This step is also illustrated in FIG. 17.

Referring again to FIG. 12B, at step 346, the inflation tube of the fillable bladder is sealed. For example, one or more ligation clips may be applied to the inflation tube to seal the tube (refer, for example, to FIGS. 1A and 1B).

Referring now to FIG. 12C, in some implementations of the method 300, step 348 may include flushing the pericardial cavity. For example, sterile saline solution can be injected and subsequently aspirated. This step can be performed to remove contrast agent substances that may have been injected earlier in the procedure. The injection and aspiration of the solution can be repeated multiple times, as desired, to flush the pericardial cavity.

At step 350, the pericardial edge management strips are removed. The removal can be performed by reversing the steps of the implementation procedure.

At step 352, excess mesh material of the implant is trimmed. This step 352, like all other steps in some implementations of the method 300, may be performed while the heart is beating. In such circumstances, the clinician can carefully gather the trailing end material of the implant in the area of the chest opening. Using a scissors or other cutting device, the clinician can trim the excess material. Care is taken to ensure a sufficient amount remains with the implant to close the implant around the apex of the heart. One non-limiting example of this step is illustrated in FIG. 18.

Referring again to FIG. 12C, at step 354 the trailing end of the implant is closed around the apex of the heart. This can be performed by suturing the trailing end portion and cinching the material together like a purse string. The inflation tube remains extending through the cinched trailing end portion. One non-limiting example of this configuration is illustrated in FIG. 1B.

Referring again to FIG. 12C, at step 356 the pericardium is loosely closed. This step can be performed by installing a few sutures (e.g., two or three) to close the pericardium. Having a loose closure will facilitate drainage of fluids form the pericardium, as is common after a procedure such as this. The inflation tube remains extending through the loosely closed pericardium.

At step 358, the end of the inflation tube is aligned in an intercostal space and the chest incision is closed. Aligning the end of the inflation tube in the intercostal space may allow future access to the inflation tube via a simple cut-down procedure through the skin adjacent to the intercostal space between the ribs (e.g., the fifth intercostal space in some implementations). Future inflation or deflation of the fillable bladder may thereby be performed with a minimally invasive access to an intercostal space under the side without extensive surgery to access the pericardium or epicardium.

A number of embodiments of the invention have been described. Nevertheless, it will be understood that various modifications may be made without departing from the scope of the invention. Accordingly, other embodiments are within the scope of the following claims.

Claims (12)

What is claimed is:
1. A cardiac implant for implantation around an exterior of a heart, the implant comprising:
an implant body comprising:
a jacket of mesh material configured for implantation circumferentially around ventricles of the heart, the jacket having an open leading end sized for positioning around an atrial-ventricular groove of the heart; and
a hem located around a perimeter of the open leading end, the hem formed from a portion of the mesh material and an elastic band surrounded by the portion of the mesh material, the circumferential length of the elastic band being less than the circumferential length of the portion of the mesh material surrounding the elastic band, the elastic band and the portion of the mesh material surrounding the elastic band having compliances selected such that the hem holds the hem of the implant body in place in the atrial-ventricular groove without interfering with cardiac blood vessel function in the region of the atrial-ventricular groove; and
a fillable bladder attached on an inside of the mesh jacket and positioned such that, when the hem is positioned around the atrial-ventricular groove, the fillable bladder is positionable on an external heart wall adjacent to a targeted heart valve structure, the fillable bladder comprising: an inner layer that, when the hem is positioned around the atrial-ventricular groove, is adjacent to the external heart wall; and an opposing outer layer that is adjacent to the mesh jacket, the inner layer of the fillable bladder having a compliance that is greater than a compliance of the outer layer such that, when the bladder is inflated, the inner layer of the bladder extends more inwardly than the outer wall extends outwardly.
2. The cardiac implant of claim 1, further comprising at least a first radiopaque marker positioned along a periphery of the fillable bladder, and at least a second radiopaque marker positioned along an exterior of the hem of the open leading end.
3. A cardiac implant for implantation around an exterior of a heart, the implant comprising:
a mesh jacket positionable circumferentially around an exterior the heart; and
a fillable bladder mounted to the mesh jacket, the fillable bladder comprising: an inner bladder layer positioned with respect to the mesh jacket so that the inner bladder layer is adjacent to a targeted exterior surface of the heat when the mesh jacket is positioned around the exterior of the heart, and an outer bladder layer positioned opposite from the inner bladder layer, the inner bladder layer having a compliance that is greater than a compliance of the outer bladder layer such that, when the mesh jacket is positioned around the exterior of the heart, the bladder expands more inwardly toward the targeted exterior surface of the heart than the bladder expands outwardly from the heart.
4. A cardiac implant system comprising:
a cardiac implant configured to be implanted around an exterior of the heart, the cardiac implant comprising an implant body, an inflatable bladder attached to the implant body, and flexible tubing in fluid communication with an internal chamber of the inflatable bladder for inflating and deflating the inflatable bladder; and
biocompatible ligation clips configured to attach to a proximal portion of the flexible tubing so as to seal an internal lumen of the flexible tubing and to reside in an intercostal space while maintaining a selected inflation state of the inflatable bladder.
5. A cardiac implant comprising:
a mesh jacket configured to circumferentially extend around an exterior portion of a heart;
a fillable bladder attached on an interior side of the mesh jacket and positioned relative to a leading end of the mesh jacket such that, when the mesh jacket circumferentially extends around the exterior portion of the heart, the fillable bladder is positionable against an external heart wall adjacent to a targeted valve structure, the fillable bladder comprising: (i) an inner layer configured to engage with the external heart wall, and (ii) an outer layer positioned between the inner layer and the mesh jacket; and
one or more radiopaque markers attached to an exterior side of the mesh jacket at a location wherein the fillable bladder is on an opposite side of the mesh jacket from the one or more radiopaque markers, the one or more radiopaque markers attached to the fillable bladder through interstitial spaces of the mesh jacket.
6. The cardiac implant of claim 5, wherein the one or more radiopaque markers are positioned to identify a peripheral sealed region of the fillable bladder.
7. The cardiac implant of claim 5, wherein the one or more radiopaque markers comprise an adhesive, and wherein the attachment of the one or more radiopaque markers to the mesh jacket and to the fillable bladder comprises an adherence of the adhesive to the mesh jacket and to the fillable baller.
8. A cardiac implant, comprising:
an implant body comprising a mesh material, the implant body comprising a distal leading end portion defining an open leading end configured to be positioned adjacent an atrial-ventricular groove of a heart, and a proximal trailing end portion configured to be positioned adjacent an apex of the heart and having a diameter that is less than a diameter of the open leading end;
a fillable bladder attached to the implant body; and
a fluid inflation tube attached to the fillable bladder and in fluid communication with the fillable bladder, wherein the fluid inflation tube extends from the fillable bladder toward the proximal trailing end portion.
9. The implant of claim 8, wherein the fillable bladder defines a chamber between a first sheet component and a second sheet component, and wherein an end portion of the fluid inflation tube is sealed between the first sheet component and the second sheet component such that a lumen defined by the fluid inflation tube is in fluid communication with the chamber.
10. The implant of claim 8, wherein the fillable bladder is spaced proximally away from the open leading end of the leading end portion such that, when the leading end portion is positioned in an atrial-ventricular groove, the fillable bladder is positioned on an exterior of a ventricle wall.
11. The implant of claim 8, further comprising at least a first radiopaque marker positioned along a periphery of the fillable bladder, and at least a second radiopaque marker positioned along a periphery of the distal leading end portion proximate to the open leading end.
12. The implant of claim 8, wherein the fluid inflation tube has a length such that a distal end of the fluid inflation tube can be located in an intercostal space for post-implantation accessibility.
US14053587 2012-10-12 2013-10-14 Cardiac treatment system and method Active 2034-03-06 US9421102B2 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US201261713351 true 2012-10-12 2012-10-12
US14053587 US9421102B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system and method

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US14053587 US9421102B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system and method
US15234126 US9844437B2 (en) 2012-10-12 2016-08-11 Cardiac treatment system and method

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US15234126 Continuation US9844437B2 (en) 2012-10-12 2016-08-11 Cardiac treatment system and method

Publications (2)

Publication Number Publication Date
US20140107405A1 true US20140107405A1 (en) 2014-04-17
US9421102B2 true US9421102B2 (en) 2016-08-23

Family

ID=50475941

Family Applications (6)

Application Number Title Priority Date Filing Date
US14053590 Active 2034-04-29 US9370425B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system and method
US14053261 Active 2034-07-10 US9421101B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system
US14053587 Active 2034-03-06 US9421102B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system and method
US15162029 Pending US20160262890A1 (en) 2012-10-12 2016-05-23 Cardiac treatment system and method
US15218675 Pending US20160331880A1 (en) 2012-10-12 2016-07-25 Cardiac treatment system
US15234126 Active US9844437B2 (en) 2012-10-12 2016-08-11 Cardiac treatment system and method

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US14053590 Active 2034-04-29 US9370425B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system and method
US14053261 Active 2034-07-10 US9421101B2 (en) 2012-10-12 2013-10-14 Cardiac treatment system

Family Applications After (3)

Application Number Title Priority Date Filing Date
US15162029 Pending US20160262890A1 (en) 2012-10-12 2016-05-23 Cardiac treatment system and method
US15218675 Pending US20160331880A1 (en) 2012-10-12 2016-07-25 Cardiac treatment system
US15234126 Active US9844437B2 (en) 2012-10-12 2016-08-11 Cardiac treatment system and method

Country Status (4)

Country Link
US (6) US9370425B2 (en)
CA (1) CA2898620A1 (en)
EP (2) EP2906143A4 (en)
WO (2) WO2014059433A3 (en)

Families Citing this family (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN103491900B (en) 2010-12-23 2017-03-01 托尔福公司 For mitral valve repair and replacement of system
CN103997990A (en) 2011-06-21 2014-08-20 托尔福公司 Prosthetic heart valve devices and associated systems and methods
US9763780B2 (en) 2011-10-19 2017-09-19 Twelve, Inc. Devices, systems and methods for heart valve replacement
US9039757B2 (en) 2011-10-19 2015-05-26 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
US9655722B2 (en) 2011-10-19 2017-05-23 Twelve, Inc. Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods
US9579198B2 (en) 2012-03-01 2017-02-28 Twelve, Inc. Hydraulic delivery systems for prosthetic heart valve devices and associated methods
JP6001280B2 (en) * 2012-03-09 2016-10-05 学校法人金沢医科大学 Method of manufacturing a heart correction net
DE102013200151A1 (en) * 2013-01-08 2014-07-10 AdjuCor GmbH Cardiac assist device with markings
CA2962240A1 (en) * 2014-09-23 2016-03-31 Health Research, Inc. Pressurized anatomical compressor for kidney device
US9737203B1 (en) * 2017-02-22 2017-08-22 Sulang Rosado Anti-slip speculum grip and methods of using same

Citations (222)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE324524C (en) 1919-06-13 1920-08-31 Siemens Schuckertwerke Gmbh A device for generating blood stasis
US1682119A (en) 1928-08-28 Cleaning device
US1965542A (en) 1933-11-24 1934-07-03 Jr William Colvin Fabric
US1982207A (en) 1933-12-29 1934-11-27 Henry D Furniss Clamping instrument and process of using the same
US2138603A (en) 1936-10-06 1938-11-29 Du Pont Explosive package
US2278926A (en) 1941-02-15 1942-04-07 Metal Textile Corp Knitted metallic fabric for belting and other uses
US2376442A (en) 1943-07-07 1945-05-22 Mehler Hugo Tubular netting
US2992550A (en) 1959-05-13 1961-07-18 Hagin Frith & Sons Knitted mesh
US3384530A (en) 1964-07-31 1968-05-21 Plastic Textile Access Ltd Extruded plastic net, method of making the same and sack made of said net
US3452742A (en) 1966-05-31 1969-07-01 Us Catheter & Instr Corp Controlled vascular curvable spring guide
US3551543A (en) 1967-09-06 1970-12-29 Plastic Textile Access Ltd Manufacture of plastic net
US3587567A (en) 1968-12-20 1971-06-28 Peter Paul Schiff Mechanical ventricular assistance assembly
US3732662A (en) 1971-07-30 1973-05-15 F Paxton Method of forming, filling, closing and labelling tubular netting bags
US3768643A (en) 1971-07-27 1973-10-30 Manetti M Nestable net produce bag and carrier therefor
US3811411A (en) 1973-01-02 1974-05-21 H Moeller Method of cultivating mollusks
US3983863A (en) 1975-06-02 1976-10-05 American Hospital Supply Corporation Heart support for coronary artery surgery
US4048990A (en) 1976-09-17 1977-09-20 Goetz Robert H Heart massage apparatus
US4196534A (en) 1977-10-27 1980-04-08 Toshitsune Shibamoto Plastic net bag and label
US4403604A (en) 1982-05-13 1983-09-13 Wilkinson Lawrence H Gastric pouch
US4428375A (en) 1982-02-16 1984-01-31 Ellman Barry R Surgical bag for splenorrhaphy
USD273514S (en) 1980-08-05 1984-04-17 Mieczyslaw Mirowski Implantable defibrillator patch electrode or similar article
US4466331A (en) 1983-06-06 1984-08-21 Redden Net Co., Inc. Method of forming twisted multiple strand synthetic twine, twines produced thereby, and fishnets formed thereof
US4536893A (en) 1982-03-03 1985-08-27 Roberto Parravicini Implant device for substaining the activity of the myocardium
JPS60203250A (en) 1984-03-29 1985-10-14 Nippon Zeon Co Patch for heart operation
US4567900A (en) 1984-06-04 1986-02-04 Moore J Paul Internal deployable defibrillator electrode
US4598039A (en) 1984-07-02 1986-07-01 At&T Bell Laboratories Formation of features in optical material
US4630597A (en) 1984-04-30 1986-12-23 Adrian Kantrowitz Dynamic aortic patch for thoracic or abdominal implantation
US4637377A (en) 1985-09-20 1987-01-20 Loop Floyd D Pillow or support member for surgical use
US4690134A (en) 1985-07-01 1987-09-01 Snyders Robert V Ventricular assist device
US4790850A (en) 1986-03-14 1988-12-13 Richards Medical Company Phosthetic ligament
EP0303719A1 (en) 1987-02-23 1989-02-22 Blagoveschensky Gosudarstvenny Meditsinsky Institut Artificial pericardium
US4821723A (en) 1987-02-27 1989-04-18 Intermedics Inc. Biphasic waveforms for defibrillation
US4827932A (en) 1987-02-27 1989-05-09 Intermedics Inc. Implantable defibrillation electrodes
US4834707A (en) 1987-09-16 1989-05-30 Evans Phillip H Venting apparatus and method for cardiovascular pumping application
US4840626A (en) 1986-09-29 1989-06-20 Johnson & Johnson Patient Care, Inc. Heparin-containing adhesion prevention barrier and process
US4878890A (en) 1986-10-15 1989-11-07 Ethicon, Inc. Perihepatic prosthesis
US4957477A (en) 1986-05-22 1990-09-18 Astra Tech Ab Heart assist jacket and method of using it
JPH02271829A (en) 1989-04-13 1990-11-06 Tanaka Kikinzoku Kogyo Kk Electrode for deciding myocardial infarction
US4973300A (en) 1989-09-22 1990-11-27 Pioneering Technologies, Inc. Cardiac sling for circumflex coronary artery surgery
US4976730A (en) 1988-10-11 1990-12-11 Kwan Gett Clifford S Artificial pericardium
US4984584A (en) 1987-01-16 1991-01-15 Riker Laboratories, Inc. High elastic modulus bandage
US4995857A (en) 1989-04-07 1991-02-26 Arnold John R Left ventricular assist device and method for temporary and permanent procedures
US5042463A (en) 1990-05-23 1991-08-27 Siemens-Pacesetter, Inc. Patch electrode for heart defibrillator
US5057117A (en) 1989-04-27 1991-10-15 The Research Foundation Of State University Of New York Method and apparatus for hemostasis and compartmentalization of a bleeding internal bodily organ
US5074129A (en) 1989-12-26 1991-12-24 Novtex Formable fabric
US5087243A (en) 1990-06-18 1992-02-11 Boaz Avitall Myocardial iontophoresis
US5131905A (en) 1990-07-16 1992-07-21 Grooters Ronald K External cardiac assist device
US5150706A (en) 1991-08-15 1992-09-29 Cox James L Cooling net for cardiac or transplant surgery
US5186711A (en) 1989-03-07 1993-02-16 Albert Einstein College Of Medicine Of Yeshiva University Hemostasis apparatus and method
US5188813A (en) 1988-10-12 1993-02-23 Johnson Matthey Public Limited Company Metal fabrics
WO1993003685A1 (en) 1991-08-19 1993-03-04 Mark Allen Eberbach Surgical apparatus and method
US5192314A (en) 1991-12-12 1993-03-09 Daskalakis Michael K Synthetic intraventricular implants and method of inserting
US5207725A (en) 1991-03-05 1993-05-04 Pinkerton Linda L Soap holder
US5224363A (en) 1988-12-16 1993-07-06 Golden Needles Knitting & Glove Co., Inc. Method of making garment, garment, and strand material
EP0557964A1 (en) 1992-02-24 1993-09-01 United States Surgical Corporation Articulating mesh deployment apparatus
US5256132A (en) 1992-08-17 1993-10-26 Snyders Robert V Cardiac assist envelope for endoscopic application
US5279539A (en) 1992-08-17 1994-01-18 Ethicon, Inc. Drawstring surgical pouch and method of use for preventing ovarian adhesions
US5290217A (en) 1991-10-10 1994-03-01 Earl K. Sipes Method and apparatus for hernia repair
US5336253A (en) 1993-02-23 1994-08-09 Medtronic, Inc. Pacing and cardioversion lead systems with shared lead conductors
US5339657A (en) 1992-09-01 1994-08-23 Mcmurray Fabrics, Inc. Net having different size openings and method of making
US5341815A (en) 1993-03-25 1994-08-30 Ethicon, Inc. Endoscopic surgical pouch
US5356432A (en) 1993-02-05 1994-10-18 C. R. Bard, Inc. Implantable mesh prosthesis and method for repairing muscle or tissue wall defects
US5366460A (en) 1990-10-11 1994-11-22 Cook Incorporated Apparatus and method for laparoscope hernia repair
US5383840A (en) 1992-07-28 1995-01-24 Vascor, Inc. Biocompatible ventricular assist and arrhythmia control device including cardiac compression band-stay-pad assembly
US5385156A (en) 1993-08-27 1995-01-31 Rose Health Care Systems Diagnostic and treatment method for cardiac rupture and apparatus for performing the same
US5405360A (en) 1992-02-24 1995-04-11 United States Surgical Corporation Resilient arm mesh deployer
US5409703A (en) 1993-06-24 1995-04-25 Carrington Laboratories, Inc. Dried hydrogel from hydrophilic-hygroscopic polymer
US5429584A (en) 1990-11-09 1995-07-04 Mcgill University Cardiac assist method and apparatus
DE29517393U1 (en) 1995-11-03 1996-02-01 Hohmann Claas Dr Med Pericardial prosthesis
US5507779A (en) 1994-04-12 1996-04-16 Ventritex, Inc. Cardiac insulation for defibrillation
WO1996016601A1 (en) 1994-11-30 1996-06-06 W.L. Gore & Associates, Inc. Surgical device for protecting organs from formation of adhesions
US5524633A (en) 1991-11-25 1996-06-11 Advanced Surgical, Inc. Self-deploying isolation bag
US5533958A (en) 1993-06-17 1996-07-09 Wilk; Peter J. Intrapericardial assist device and associated method
WO1996031175A1 (en) 1995-04-01 1996-10-10 Smith & Nephew Plc Fabric article with extension indicator
US5593441A (en) 1992-03-04 1997-01-14 C. R. Bard, Inc. Method for limiting the incidence of postoperative adhesions
US5603337A (en) 1994-12-05 1997-02-18 Jarvik; Robert Two-stage cardiomyoplasty
US5611515A (en) 1991-12-03 1997-03-18 Boston Scientic Corporation Bladder neck suspension procedure
US5647380A (en) 1995-06-07 1997-07-15 W. L. Gore & Associates, Inc. Method of making a left ventricular assist device
US5695525A (en) 1992-05-20 1997-12-09 C.R. Bard, Incorporated Implantable prosthesis and method and apparatus for loading and delivering an implantable prosthesis
US5702343A (en) 1996-10-02 1997-12-30 Acorn Medical, Inc. Cardiac reinforcement device
US5713954A (en) 1995-06-13 1998-02-03 Abiomed R&D, Inc. Extra cardiac ventricular assist device
US5735290A (en) 1993-02-22 1998-04-07 Heartport, Inc. Methods and systems for performing thoracoscopic coronary bypass and other procedures
US5766216A (en) 1996-05-30 1998-06-16 Gangal; Hanamraddi T. Band applicator for appendicular and meso-appendicular stumps
WO1998029041A1 (en) 1997-01-02 1998-07-09 Myocor, Inc. Heart wall tension reduction apparatus and method
US5782746A (en) 1996-02-15 1998-07-21 Wright; John T. M. Local cardiac immobilization surgical device
WO1998035632A1 (en) 1997-02-13 1998-08-20 Boston Scientific Ireland Limited Stabilization sling for use in minimally invasive pelvic surgery
US5800334A (en) 1993-06-17 1998-09-01 Wilk; Peter J. Intrapericardial assist device and associated method
US5800528A (en) 1995-06-13 1998-09-01 Abiomed R & D, Inc. Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation
US5839842A (en) 1998-02-05 1998-11-24 Lever Brothers Company, Division Of Conopco, Inc. Cleansing system including a toilet bar and sponge supported within a porous pouch
US5853422A (en) 1996-03-22 1998-12-29 Scimed Life Systems, Inc. Apparatus and method for closing a septal defect
WO1998058598A1 (en) 1997-06-21 1998-12-30 Hans Haindl Bag for at least partially enveloping a heart
US5928250A (en) 1997-01-30 1999-07-27 Nissho Corporation Catheter assembly for intracardiac suture
US5931810A (en) 1996-12-05 1999-08-03 Comedicus Incorporated Method for accessing the pericardial space
WO1999044534A1 (en) 1998-03-05 1999-09-10 The University Of Cincinnati Device and method for restructuring heart chamber geometry
US5961440A (en) 1997-01-02 1999-10-05 Myocor, Inc. Heart wall tension reduction apparatus and method
WO1999052470A1 (en) 1998-04-10 1999-10-21 Cardio Technologies, Inc. Cardiac remodeling and reinforcement device
WO1999052471A1 (en) 1998-04-11 1999-10-21 Intermedics Inc. Vascular and endoluminal stents with iridium oxide coating
US5972013A (en) 1997-09-19 1999-10-26 Comedicus Incorporated Direct pericardial access device with deflecting mechanism and method
US5976551A (en) 1991-11-15 1999-11-02 Institut Pasteur And Institut Nationale De La Sante Et De La Recherche Medicale Altered major histocompatibility complex (MHC) determinant and method of using the determinant
US5990378A (en) 1995-05-25 1999-11-23 Bridport Gundry (Uk) Limited Textile surgical implants
WO2000001306A1 (en) 1998-07-07 2000-01-13 Pulsecare Ltd. Minimal invasive cardiac massage device
WO2000002500A1 (en) 1998-07-13 2000-01-20 Acorn Cardiovascular, Inc. Cardiac disease treatment device and method
US6042536A (en) 1998-08-13 2000-03-28 Contimed, Inc. Bladder sling
WO2000016700A1 (en) 1998-09-21 2000-03-30 Myocor, Inc. External stress reduction device and method
US6045497A (en) 1997-01-02 2000-04-04 Myocor, Inc. Heart wall tension reduction apparatus and method
WO2000028912A1 (en) 1998-11-18 2000-05-25 Acorn Cardiovascular, Inc. Cardiac constraint with prior venus occlusion
WO2000028918A1 (en) 1998-11-18 2000-05-25 Acorn Cardiovascular, Inc. Defibrillating cardiac constraint
US6076013A (en) 1999-01-14 2000-06-13 Brennan; Edward F. Apparatus and methods for treating congestive heart failure
US6077214A (en) 1998-07-29 2000-06-20 Myocor, Inc. Stress reduction apparatus and method
US6085754A (en) 1998-07-13 2000-07-11 Acorn Cardiovascular, Inc. Cardiac disease treatment method
US6089051A (en) 1993-01-14 2000-07-18 W.C. Heraeus Gmbh Warp-knit fabric of noble metal-containing wires, and method for the production thereof
WO2000006028A9 (en) 1998-07-29 2000-08-10 Myocor Inc Transventricular implant tools and devices
US6123662A (en) 1998-07-13 2000-09-26 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6155972A (en) 1999-02-02 2000-12-05 Acorn Cardiovascular, Inc. Cardiac constraint jacket construction
US6155968A (en) 1998-07-23 2000-12-05 Wilk; Peter J. Method and device for improving cardiac function
WO2001002500A1 (en) 1999-06-30 2001-01-11 Basf Coatings Ag Coating material and its use for producing filler coats and stone impact protection primers
US6174279B1 (en) 1999-09-21 2001-01-16 Acorn Cardiovascular, Inc. Cardiac constraint with tension indicator
WO2001003608A1 (en) 1999-07-07 2001-01-18 Acorn Cardiovascular, Inc. Cardiac reinforcement devices and methods
US6179791B1 (en) 1999-09-21 2001-01-30 Acorn Cardiovascular, Inc. Device for heart measurement
WO2001010421A1 (en) 1999-08-06 2001-02-15 Board Of Regents, The University Of Texas System Drug releasing biodegradable fiber implant
US6193646B1 (en) 1995-08-16 2001-02-27 Hk Medical Technologies Incorporated Intraurethral bladder control device with retainer apparatus
US6193648B1 (en) 1999-09-21 2001-02-27 Acorn Cardiovascular, Inc. Cardiac constraint with draw string tensioning
US6205747B1 (en) 1997-02-07 2001-03-27 Rosalina Paniagua Olaechea Process for closing nets for fruits and the like and net closed by means of said process
US6206820B1 (en) 1995-10-18 2001-03-27 Fraunhofer Gesellschaft Zur Foerderung Der Angewandten Forschung Device for supporting cardiac function having elastic filling chambers
US6206004B1 (en) 1996-12-06 2001-03-27 Comedicus Incorporated Treatment method via the pericardial space
US6221103B1 (en) 1996-01-02 2001-04-24 The University Of Cincinnati Device and method for restructuring heart chamber geometry
WO2001067985A1 (en) 2000-03-10 2001-09-20 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6293906B1 (en) 2000-01-14 2001-09-25 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US6332893B1 (en) 1997-12-17 2001-12-25 Myocor, Inc. Valve to myocardium tension members device and method
US6360749B1 (en) 1998-10-09 2002-03-26 Swaminathan Jayaraman Modification of properties and geometry of heart tissue to influence heart function
US20020068850A1 (en) 2000-12-01 2002-06-06 Acorn Cardiovascular, Inc. Apparatus and method for delivery of cardiac constraint jacket
US6406420B1 (en) 1997-01-02 2002-06-18 Myocor, Inc. Methods and devices for improving cardiac function in hearts
WO2001091667A9 (en) 2000-05-31 2002-07-04 Cardioclasp Inc Devices and methods for assisting natural heart function
US6425856B1 (en) 2000-05-10 2002-07-30 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6432039B1 (en) 1998-12-21 2002-08-13 Corset, Inc. Methods and apparatus for reinforcement of the heart ventricles
US20020147406A1 (en) 2001-04-02 2002-10-10 Von Segesser Ludwig K. Cardiac stabilizers and methods of use thereof
US20020169360A1 (en) 1998-07-16 2002-11-14 Cardiothoracic Systems, Inc., A California Corporation Surgical procedures and devices for increasing cardiac output of the heart
US6482146B1 (en) 2000-06-13 2002-11-19 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6488618B1 (en) 1999-04-16 2002-12-03 Coroneo, Inc. Coronary stabilizer for performing beating heart surgery
US6494825B1 (en) 1998-04-22 2002-12-17 Scimed Life Systems, Inc. System for stress relieving the heart muscle and for controlling heart function
WO2002013726A3 (en) 2000-08-17 2003-01-23 Acorn Cardiovascular Inc Cardiac disease treatment and device
US6517570B1 (en) 1994-08-31 2003-02-11 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6520904B1 (en) 1996-01-02 2003-02-18 The University Of Cincinnati Device and method for restructuring heart chamber geometry
WO2002000099A9 (en) 2000-06-23 2003-03-06 Viacor Inc Automated annular plication for mitral valve repair
US20030050529A1 (en) 2000-03-21 2003-03-13 Myocor, Inc. Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly
US20030060895A1 (en) 2001-09-25 2003-03-27 French Ronald G. Pericardium reinforcing devices and methods of using them
US6541678B2 (en) 1999-09-27 2003-04-01 Brennen Medical, Inc. Immunostimulating coating for surgical devices
US6547716B1 (en) 2000-11-28 2003-04-15 Abiomed, Inc. Passive cardiac restraint systems having multiple layers of inflatable elements
US6558319B1 (en) 1998-09-30 2003-05-06 A-Med Systems, Inc. Heart stabilizer apparatus
US20030088149A1 (en) 2001-09-07 2003-05-08 Raman Jaishankar Method and apparatus for external stabilization of the heart
US6564094B2 (en) 2000-12-22 2003-05-13 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6569082B1 (en) 1999-08-10 2003-05-27 Origin Medsystems, Inc. Apparatus and methods for cardiac restraint
US6575921B2 (en) 2001-02-09 2003-06-10 Acorn Cardiovascular, Inc. Device for heart measurement
US6587734B2 (en) 1998-11-04 2003-07-01 Acorn Cardiovascular, Inc. Cardio therapeutic heart sack
US20030130731A1 (en) 2002-01-09 2003-07-10 Myocor, Inc. Devices and methods for heart valve treatment
US6592514B2 (en) 2001-05-15 2003-07-15 Ethicon, Inc. Organ retraction tape positioner and method for retracting and positioning an internal organ
US6612978B2 (en) 1999-12-22 2003-09-02 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6616596B1 (en) 2000-11-28 2003-09-09 Abiomed, Inc. Cardiac assistance systems having multiple layers of inflatable elements
US6616684B1 (en) 2000-10-06 2003-09-09 Myocor, Inc. Endovascular splinting devices and methods
US6620095B2 (en) 2000-12-22 2003-09-16 Syde A. Taheri Cradle-assisted myocardial repair and treatment
US6622730B2 (en) 2001-03-30 2003-09-23 Myocor, Inc. Device for marking and aligning positions on the heart
US20030229265A1 (en) 2000-06-13 2003-12-11 Girard Michael J. Cardiac support device
US20030229260A1 (en) 2002-06-05 2003-12-11 Acorn Cardiovascular, Inc. Cardiac support device with tension indicator
US20030233023A1 (en) 2000-09-23 2003-12-18 Harefield Cardiac Limited Blood circulation assistance device
US20040002626A1 (en) 2001-07-16 2004-01-01 Yair Feld In-vivo method and device for improving diastolic function of the left ventricle
US6673009B1 (en) 2000-11-08 2004-01-06 Acorn Cardiovascular, Inc. Adjustment clamp
US20040010180A1 (en) * 2002-05-16 2004-01-15 Scorvo Sean K. Cardiac assist system
US6682475B2 (en) * 2002-06-11 2004-01-27 Acorn Cardiovascular, Inc. Tension indicator for cardiac support device and method therefore
US6685627B2 (en) 1998-10-09 2004-02-03 Swaminathan Jayaraman Modification of properties and geometry of heart tissue to influence heart function
US20040034272A1 (en) 2001-02-09 2004-02-19 Diaz Cesar M. Minimally invasive ventricular assist technology and method
US6695768B1 (en) 1999-03-30 2004-02-24 Robert A. Levine Adjustable periventricular ring/ring like device/method for control of ischemic mitral regurgitation and congestive heart disease
US6695769B2 (en) 2001-09-25 2004-02-24 The Foundry, Inc. Passive ventricular support devices and methods of using them
US6701929B2 (en) 1999-03-03 2004-03-09 Hany Hussein Device and method for treatment of congestive heart failure
US6709382B1 (en) 1999-05-04 2004-03-23 Simon Marcus Horner Cardiac assist method and apparatus
US6723041B2 (en) 2001-09-10 2004-04-20 Lilip Lau Device for treating heart failure
US6723038B1 (en) 2000-10-06 2004-04-20 Myocor, Inc. Methods and devices for improving mitral valve function
US6726696B1 (en) 2001-04-24 2004-04-27 Advanced Catheter Engineering, Inc. Patches and collars for medical applications and methods of use
US6726920B1 (en) 2000-09-22 2004-04-27 Durect Corporation Implantable drug delivery patch
US6730016B1 (en) 2000-06-12 2004-05-04 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6755861B2 (en) 2001-10-16 2004-06-29 Granit Medical Innovation, Inc. Device for providing a portion of an organism with a desired shape
US20040133062A1 (en) 2002-10-11 2004-07-08 Suresh Pai Minimally invasive cardiac force transfer structures
US20040147805A1 (en) 2002-01-07 2004-07-29 Lilip Lau Cardiac harness
US20040147965A1 (en) 1999-06-07 2004-07-29 The Johns Hopkins University Cardiac shock electrode system and corresponding implantable defibrillator system
US6776754B1 (en) 2000-10-04 2004-08-17 Wilk Patent Development Corporation Method for closing off lower portion of heart ventricle
US20040181118A1 (en) 1998-03-17 2004-09-16 Kochamba Gary S. Tissue stabilization
US20040210104A1 (en) 2002-11-15 2004-10-21 Lilip Lau Cardiac harness delivery device and method
US20040215308A1 (en) 2000-09-18 2004-10-28 Cameron Health, Inc. Subcutaneous electrode with improved contact shape for transthoracic conduction
US20040249242A1 (en) 2003-03-28 2004-12-09 Lilip Lau Multi-panel cardiac harness
US20050010079A1 (en) 2002-12-06 2005-01-13 Estech, Inc. Methods and devices for cardiac surgery
US6852076B2 (en) 1999-08-09 2005-02-08 Cardiokinetix, Inc. Method for improving cardiac function
US6852075B1 (en) 1996-02-20 2005-02-08 Cardiothoracic Systems, Inc. Surgical devices for imposing a negative pressure to stabilize cardiac tissue during surgery
US20050033109A1 (en) 2001-10-31 2005-02-10 Lilip Lau Heart failure treatment device and method
US6858001B1 (en) 1997-07-11 2005-02-22 A-Med Systems, Inc. Single port cardiac support apparatus
US20050054892A1 (en) 2003-07-10 2005-03-10 Lilip Lau Self-anchoring cardiac harness
US20050059855A1 (en) 2002-11-15 2005-03-17 Lilip Lau Cardiac harness delivery device and method
US20050059854A1 (en) 2003-09-16 2005-03-17 Acorn Cardiovascular, Inc. Apparatus and method for applying cardiac support device
US6902522B1 (en) 2000-06-12 2005-06-07 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US20050133941A1 (en) 2003-08-21 2005-06-23 Elringklinger Ag Tube with a marking and process for the production of a marking on a tube
US20050171589A1 (en) 2003-11-07 2005-08-04 Lilip Lau Cardiac harness and method of delivery by minimally invasive access
US20050192474A1 (en) 2004-03-01 2005-09-01 Acorn Cardiovascular, Inc. Seam closure device and methods
US20050256368A1 (en) 2002-11-15 2005-11-17 Paracor Medical, Inc. Introducer for a cardiac harness delivery
US20050283042A1 (en) 2003-03-28 2005-12-22 Steve Meyer Cardiac harness having radiopaque coating and method of use
US20050288715A1 (en) 2003-11-07 2005-12-29 Lilip Lau Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing
US20060009831A1 (en) 2003-11-07 2006-01-12 Lilip Lau Cardiac harness having leadless electrodes for pacing and sensing therapy
US20060063970A1 (en) 2002-09-06 2006-03-23 Mardil, Inc. Method and apparatus for external stabilization of the heart valves and myocardium
US7112219B2 (en) 2002-11-12 2006-09-26 Myocor, Inc. Devices and methods for heart valve treatment
US20060229490A1 (en) 1999-08-10 2006-10-12 Chin Albert K Method for cardiac restaint
US20060270896A1 (en) 2005-05-31 2006-11-30 Ethicon, Inc. Method and device for deployment of a sub-pericardial sack
US7155295B2 (en) 2003-11-07 2006-12-26 Paracor Medical, Inc. Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing
US20070032696A1 (en) 2005-07-22 2007-02-08 Sieu Duong Cardiac harness delivery device
US7181272B2 (en) 2002-04-22 2007-02-20 Medtronic, Inc. Cardiac restraint with electrode attachment sites
US20070043416A1 (en) 2005-08-19 2007-02-22 Cardiac Pacemakers, Inc. Implantable electrode array
WO2006023580A3 (en) 2004-08-16 2007-04-12 Brigham & Womens Hospital Cardiac restraint
US20070208215A1 (en) 2006-03-03 2007-09-06 Acorn Cardiovascular, Inc. Self-adjusting securing structure for a cardiac support device
WO2008011411A2 (en) 2006-07-17 2008-01-24 Acorn Cardiovascular, Inc. Cardiac support device delivery tool with release mechanism
US20080064917A1 (en) 2003-10-15 2008-03-13 Eli Bar Amplification-Based Cardiac Assist Device
US7468029B1 (en) 2001-06-04 2008-12-23 Robertson Jr Abel L Progressive biventricular diastolic support device
US20090062596A1 (en) 2007-09-05 2009-03-05 Leinsing Karl R Heart band with fillable chambers to modify heart valve function
US20090131743A1 (en) 2006-06-29 2009-05-21 Acorn Cardiovascular, Inc. Low friction delivery tool for a cardiac support device
US20100004504A1 (en) 2008-07-01 2010-01-07 Maquet Cardiovascular Llc Epicardial clip
WO2010111592A1 (en) 2009-03-27 2010-09-30 Acorn Cardiovascular, Inc. Intra-operative heart size measuring tool
US20100268019A1 (en) 2006-03-03 2010-10-21 Acorn Cardiovascular, Inc. Cadiac support device delivery tool with independently movable arms

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4035849A (en) * 1975-11-17 1977-07-19 William W. Angell Heart valve stent and process for preparing a stented heart valve prosthesis
DE4317752C2 (en) * 1993-05-27 1997-10-16 Peter Dr Feindt Device for supporting the cardiac function
US5571088A (en) * 1993-07-01 1996-11-05 Boston Scientific Corporation Ablation catheters
US6918870B1 (en) * 1999-06-17 2005-07-19 Heart Assist Technologies Pty Ltd Assist device for the failing heart
WO2004002364A3 (en) 2002-06-27 2005-07-28 J Luis Guerrero Ventricular remodeling for artioventricular valve regurgitation
US20070255093A1 (en) * 2002-11-15 2007-11-01 Lilip Lau Cardiac harness delivery device and method
CA2505760A1 (en) * 2002-11-15 2004-06-03 Pressure Products Medical Supplies, Inc. A method and apparatus for anchoring of pacing leads
US20050058853A1 (en) 2003-09-15 2005-03-17 Eastman Kodak Company Green organic light-emitting diodes
US20050197527A1 (en) * 2004-03-04 2005-09-08 Bolling Steven F. Adjustable heart constraining apparatus and method therefore
US20060004249A1 (en) * 2004-06-30 2006-01-05 Ethicon Incorporated Systems and methods for sizing cardiac assist device
US20070208217A1 (en) * 2006-03-03 2007-09-06 Acorn Cardiovascular, Inc. Self-adjusting attachment structure for a cardiac support device
EP3150171A1 (en) * 2007-05-15 2017-04-05 JenaValve Technology, Inc. Handle for manipulating a catheter tip, catheter system and medical insertion system for inserting a self-expandalbe heart valve stent
US20100286480A1 (en) * 2009-05-06 2010-11-11 Peine William J Surgical instrument
WO2011069538A1 (en) * 2009-12-08 2011-06-16 St. Jude Medical Ab Implantable medical device for cardiac therapy

Patent Citations (367)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1682119A (en) 1928-08-28 Cleaning device
DE324524C (en) 1919-06-13 1920-08-31 Siemens Schuckertwerke Gmbh A device for generating blood stasis
US1965542A (en) 1933-11-24 1934-07-03 Jr William Colvin Fabric
US1982207A (en) 1933-12-29 1934-11-27 Henry D Furniss Clamping instrument and process of using the same
US2138603A (en) 1936-10-06 1938-11-29 Du Pont Explosive package
US2278926A (en) 1941-02-15 1942-04-07 Metal Textile Corp Knitted metallic fabric for belting and other uses
US2376442A (en) 1943-07-07 1945-05-22 Mehler Hugo Tubular netting
US2992550A (en) 1959-05-13 1961-07-18 Hagin Frith & Sons Knitted mesh
US3384530A (en) 1964-07-31 1968-05-21 Plastic Textile Access Ltd Extruded plastic net, method of making the same and sack made of said net
US3452742A (en) 1966-05-31 1969-07-01 Us Catheter & Instr Corp Controlled vascular curvable spring guide
US3551543A (en) 1967-09-06 1970-12-29 Plastic Textile Access Ltd Manufacture of plastic net
US3587567A (en) 1968-12-20 1971-06-28 Peter Paul Schiff Mechanical ventricular assistance assembly
US3768643A (en) 1971-07-27 1973-10-30 Manetti M Nestable net produce bag and carrier therefor
US3732662A (en) 1971-07-30 1973-05-15 F Paxton Method of forming, filling, closing and labelling tubular netting bags
US3811411A (en) 1973-01-02 1974-05-21 H Moeller Method of cultivating mollusks
US3983863A (en) 1975-06-02 1976-10-05 American Hospital Supply Corporation Heart support for coronary artery surgery
US4048990A (en) 1976-09-17 1977-09-20 Goetz Robert H Heart massage apparatus
US4196534A (en) 1977-10-27 1980-04-08 Toshitsune Shibamoto Plastic net bag and label
USD273514S (en) 1980-08-05 1984-04-17 Mieczyslaw Mirowski Implantable defibrillator patch electrode or similar article
US4428375A (en) 1982-02-16 1984-01-31 Ellman Barry R Surgical bag for splenorrhaphy
US4536893A (en) 1982-03-03 1985-08-27 Roberto Parravicini Implant device for substaining the activity of the myocardium
US4403604A (en) 1982-05-13 1983-09-13 Wilkinson Lawrence H Gastric pouch
US4466331A (en) 1983-06-06 1984-08-21 Redden Net Co., Inc. Method of forming twisted multiple strand synthetic twine, twines produced thereby, and fishnets formed thereof
JPS60203250A (en) 1984-03-29 1985-10-14 Nippon Zeon Co Patch for heart operation
US4630597A (en) 1984-04-30 1986-12-23 Adrian Kantrowitz Dynamic aortic patch for thoracic or abdominal implantation
US4567900A (en) 1984-06-04 1986-02-04 Moore J Paul Internal deployable defibrillator electrode
US4598039A (en) 1984-07-02 1986-07-01 At&T Bell Laboratories Formation of features in optical material
US4690134A (en) 1985-07-01 1987-09-01 Snyders Robert V Ventricular assist device
US4637377A (en) 1985-09-20 1987-01-20 Loop Floyd D Pillow or support member for surgical use
US4790850A (en) 1986-03-14 1988-12-13 Richards Medical Company Phosthetic ligament
US4932972A (en) 1986-03-14 1990-06-12 Richards Medical Company Prosthetic ligament
US4957477A (en) 1986-05-22 1990-09-18 Astra Tech Ab Heart assist jacket and method of using it
US4840626A (en) 1986-09-29 1989-06-20 Johnson & Johnson Patient Care, Inc. Heparin-containing adhesion prevention barrier and process
US4878890A (en) 1986-10-15 1989-11-07 Ethicon, Inc. Perihepatic prosthesis
US4984584A (en) 1987-01-16 1991-01-15 Riker Laboratories, Inc. High elastic modulus bandage
EP0303719A1 (en) 1987-02-23 1989-02-22 Blagoveschensky Gosudarstvenny Meditsinsky Institut Artificial pericardium
US4936857A (en) 1987-02-23 1990-06-26 Kulik Yaroslav P Prosthetic pericardium
US4827932A (en) 1987-02-27 1989-05-09 Intermedics Inc. Implantable defibrillation electrodes
US4821723A (en) 1987-02-27 1989-04-18 Intermedics Inc. Biphasic waveforms for defibrillation
EP0280564B1 (en) 1987-02-27 1993-06-16 Intermedics, Inc. Implantable defribrillation electrodes
JPH01145066A (en) 1987-09-16 1989-06-07 Phillip H Evans Mechanically augmenting device for heart
US4834707A (en) 1987-09-16 1989-05-30 Evans Phillip H Venting apparatus and method for cardiovascular pumping application
GB2209678B (en) 1987-09-16 1992-03-25 Phillip Harrell Evans Blood gas venting apparatus
US4976730A (en) 1988-10-11 1990-12-11 Kwan Gett Clifford S Artificial pericardium
US5188813A (en) 1988-10-12 1993-02-23 Johnson Matthey Public Limited Company Metal fabrics
US5224363A (en) 1988-12-16 1993-07-06 Golden Needles Knitting & Glove Co., Inc. Method of making garment, garment, and strand material
US5186711A (en) 1989-03-07 1993-02-16 Albert Einstein College Of Medicine Of Yeshiva University Hemostasis apparatus and method
US4995857A (en) 1989-04-07 1991-02-26 Arnold John R Left ventricular assist device and method for temporary and permanent procedures
JPH02271829A (en) 1989-04-13 1990-11-06 Tanaka Kikinzoku Kogyo Kk Electrode for deciding myocardial infarction
US5057117A (en) 1989-04-27 1991-10-15 The Research Foundation Of State University Of New York Method and apparatus for hemostasis and compartmentalization of a bleeding internal bodily organ
US4973300A (en) 1989-09-22 1990-11-27 Pioneering Technologies, Inc. Cardiac sling for circumflex coronary artery surgery
US5074129A (en) 1989-12-26 1991-12-24 Novtex Formable fabric
US5042463A (en) 1990-05-23 1991-08-27 Siemens-Pacesetter, Inc. Patch electrode for heart defibrillator
US5087243A (en) 1990-06-18 1992-02-11 Boaz Avitall Myocardial iontophoresis
US5131905A (en) 1990-07-16 1992-07-21 Grooters Ronald K External cardiac assist device
US5366460A (en) 1990-10-11 1994-11-22 Cook Incorporated Apparatus and method for laparoscope hernia repair
US5429584A (en) 1990-11-09 1995-07-04 Mcgill University Cardiac assist method and apparatus
US5207725A (en) 1991-03-05 1993-05-04 Pinkerton Linda L Soap holder
US5150706A (en) 1991-08-15 1992-09-29 Cox James L Cooling net for cardiac or transplant surgery
WO1993003685A1 (en) 1991-08-19 1993-03-04 Mark Allen Eberbach Surgical apparatus and method
US5290217A (en) 1991-10-10 1994-03-01 Earl K. Sipes Method and apparatus for hernia repair
US5976551A (en) 1991-11-15 1999-11-02 Institut Pasteur And Institut Nationale De La Sante Et De La Recherche Medicale Altered major histocompatibility complex (MHC) determinant and method of using the determinant
US5524633A (en) 1991-11-25 1996-06-11 Advanced Surgical, Inc. Self-deploying isolation bag
US5611515A (en) 1991-12-03 1997-03-18 Boston Scientic Corporation Bladder neck suspension procedure
US5192314A (en) 1991-12-12 1993-03-09 Daskalakis Michael K Synthetic intraventricular implants and method of inserting
US5405360A (en) 1992-02-24 1995-04-11 United States Surgical Corporation Resilient arm mesh deployer
EP0557964A1 (en) 1992-02-24 1993-09-01 United States Surgical Corporation Articulating mesh deployment apparatus
US5593441A (en) 1992-03-04 1997-01-14 C. R. Bard, Inc. Method for limiting the incidence of postoperative adhesions
US5695525A (en) 1992-05-20 1997-12-09 C.R. Bard, Incorporated Implantable prosthesis and method and apparatus for loading and delivering an implantable prosthesis
US5558617A (en) 1992-07-28 1996-09-24 Vascor, Inc. Cardiac compression band-stay-pad assembly and method of replacing the same
US5383840A (en) 1992-07-28 1995-01-24 Vascor, Inc. Biocompatible ventricular assist and arrhythmia control device including cardiac compression band-stay-pad assembly
US5256132A (en) 1992-08-17 1993-10-26 Snyders Robert V Cardiac assist envelope for endoscopic application
US5279539A (en) 1992-08-17 1994-01-18 Ethicon, Inc. Drawstring surgical pouch and method of use for preventing ovarian adhesions
US5339657A (en) 1992-09-01 1994-08-23 Mcmurray Fabrics, Inc. Net having different size openings and method of making
US6089051A (en) 1993-01-14 2000-07-18 W.C. Heraeus Gmbh Warp-knit fabric of noble metal-containing wires, and method for the production thereof
US5356432B1 (en) 1993-02-05 1997-02-04 Bard Inc C R Implantable mesh prosthesis and method for repairing muscle or tissue wall defects
US5356432A (en) 1993-02-05 1994-10-18 C. R. Bard, Inc. Implantable mesh prosthesis and method for repairing muscle or tissue wall defects
US5735290A (en) 1993-02-22 1998-04-07 Heartport, Inc. Methods and systems for performing thoracoscopic coronary bypass and other procedures
US5336253A (en) 1993-02-23 1994-08-09 Medtronic, Inc. Pacing and cardioversion lead systems with shared lead conductors
US5341815A (en) 1993-03-25 1994-08-30 Ethicon, Inc. Endoscopic surgical pouch
US5533958A (en) 1993-06-17 1996-07-09 Wilk; Peter J. Intrapericardial assist device and associated method
US5800334A (en) 1993-06-17 1998-09-01 Wilk; Peter J. Intrapericardial assist device and associated method
US5409703A (en) 1993-06-24 1995-04-25 Carrington Laboratories, Inc. Dried hydrogel from hydrophilic-hygroscopic polymer
US5385156A (en) 1993-08-27 1995-01-31 Rose Health Care Systems Diagnostic and treatment method for cardiac rupture and apparatus for performing the same
US5507779A (en) 1994-04-12 1996-04-16 Ventritex, Inc. Cardiac insulation for defibrillation
US6517570B1 (en) 1994-08-31 2003-02-11 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
WO1996016601A1 (en) 1994-11-30 1996-06-06 W.L. Gore & Associates, Inc. Surgical device for protecting organs from formation of adhesions
US5603337A (en) 1994-12-05 1997-02-18 Jarvik; Robert Two-stage cardiomyoplasty
WO1996031175A1 (en) 1995-04-01 1996-10-10 Smith & Nephew Plc Fabric article with extension indicator
US5990378A (en) 1995-05-25 1999-11-23 Bridport Gundry (Uk) Limited Textile surgical implants
US5647380A (en) 1995-06-07 1997-07-15 W. L. Gore & Associates, Inc. Method of making a left ventricular assist device
US6508756B1 (en) 1995-06-13 2003-01-21 Abiomed, Inc. Passive cardiac assistance device
US6224540B1 (en) 1995-06-13 2001-05-01 Abiomed, Inc. Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation
US5713954A (en) 1995-06-13 1998-02-03 Abiomed R&D, Inc. Extra cardiac ventricular assist device
US5800528A (en) 1995-06-13 1998-09-01 Abiomed R & D, Inc. Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation
US6193646B1 (en) 1995-08-16 2001-02-27 Hk Medical Technologies Incorporated Intraurethral bladder control device with retainer apparatus
US6206820B1 (en) 1995-10-18 2001-03-27 Fraunhofer Gesellschaft Zur Foerderung Der Angewandten Forschung Device for supporting cardiac function having elastic filling chambers
DE29517393U1 (en) 1995-11-03 1996-02-01 Hohmann Claas Dr Med Pericardial prosthesis
US6520904B1 (en) 1996-01-02 2003-02-18 The University Of Cincinnati Device and method for restructuring heart chamber geometry
US6221103B1 (en) 1996-01-02 2001-04-24 The University Of Cincinnati Device and method for restructuring heart chamber geometry
US5782746A (en) 1996-02-15 1998-07-21 Wright; John T. M. Local cardiac immobilization surgical device
US20050038316A1 (en) 1996-02-20 2005-02-17 Taylor Charles S. Surgical devices for imposing a negative pressure to stabilize cardiac tissue during surgery
US6852075B1 (en) 1996-02-20 2005-02-08 Cardiothoracic Systems, Inc. Surgical devices for imposing a negative pressure to stabilize cardiac tissue during surgery
US5853422A (en) 1996-03-22 1998-12-29 Scimed Life Systems, Inc. Apparatus and method for closing a septal defect
US5766216A (en) 1996-05-30 1998-06-16 Gangal; Hanamraddi T. Band applicator for appendicular and meso-appendicular stumps
US6375608B1 (en) 1996-10-02 2002-04-23 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US7163507B2 (en) 1996-10-02 2007-01-16 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US6077218A (en) 1996-10-02 2000-06-20 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US6544168B2 (en) 1996-10-02 2003-04-08 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US20040181124A1 (en) 1996-10-02 2004-09-16 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US6893392B2 (en) 1996-10-02 2005-05-17 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US20040059181A1 (en) 1996-10-02 2004-03-25 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US5702343A (en) 1996-10-02 1997-12-30 Acorn Medical, Inc. Cardiac reinforcement device
US6165121A (en) 1996-10-02 2000-12-26 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US6165122A (en) 1996-10-02 2000-12-26 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US20070225547A1 (en) 1996-10-02 2007-09-27 Acorn Cardiovascular, Inc. Collapsible delivery tool for cardiac support device
US6126590A (en) 1996-10-02 2000-10-03 Acorn Cardiovascular, Inc. Cardiac reinforcement device
US7351200B2 (en) 1996-10-02 2008-04-01 Acorn Cardiovascular, Inc. Cardiac reinforcement device
WO1998014136A1 (en) 1996-10-02 1998-04-09 Acorn Cardiovascular, Inc. Heart volume limiting device
US5931810A (en) 1996-12-05 1999-08-03 Comedicus Incorporated Method for accessing the pericardial space
US6206004B1 (en) 1996-12-06 2001-03-27 Comedicus Incorporated Treatment method via the pericardial space
US20020068849A1 (en) 1997-01-02 2002-06-06 Myocor, Inc. Heart wall tension reduction apparatus
US20030166992A1 (en) 1997-01-02 2003-09-04 Myocor, Inc. Heart wall tension reduction apparatus
US20030171641A1 (en) 1997-01-02 2003-09-11 Myocor, Inc Heart wall tension reduction apparatus and method
US6629921B1 (en) 1997-01-02 2003-10-07 Myocor, Inc. Heart wall tension reduction apparatus and method
US6261222B1 (en) 1997-01-02 2001-07-17 Myocor, Inc. Heart wall tension reduction apparatus and method
WO1998029041A1 (en) 1997-01-02 1998-07-09 Myocor, Inc. Heart wall tension reduction apparatus and method
US6332863B1 (en) 1997-01-02 2001-12-25 Myocor, Inc. Heart wall tension reduction kit
US6514194B2 (en) 1997-01-02 2003-02-04 Myocor, Inc. Heart wall tension reduction apparatus and method
US6059715A (en) 1997-01-02 2000-05-09 Myocor, Inc. Heart wall tension reduction apparatus
US6589160B2 (en) 1997-01-02 2003-07-08 Myocor, Inc. Heart wall tension reduction apparatus
US6162168A (en) 1997-01-02 2000-12-19 Myocor, Inc. Heart wall tension reduction apparatus
US6050936A (en) 1997-01-02 2000-04-18 Myocor, Inc. Heart wall tension reduction apparatus
US6165120A (en) 1997-01-02 2000-12-26 Myocor, Inc. Heart wall tension reduction apparatus and method
US6165119A (en) 1997-01-02 2000-12-26 Myocor, Inc. Heart wall tension reduction apparatus and method
US6406420B1 (en) 1997-01-02 2002-06-18 Myocor, Inc. Methods and devices for improving cardiac function in hearts
US6755777B2 (en) 1997-01-02 2004-06-29 Myocor, Inc. Heart wall tension reduction apparatus and method
US5961440A (en) 1997-01-02 1999-10-05 Myocor, Inc. Heart wall tension reduction apparatus and method
US20020169359A1 (en) 1997-01-02 2002-11-14 Myocor, Inc. Methods and devices for improving cardiac function in hearts
US6332864B1 (en) 1997-01-02 2001-12-25 Myocor, Inc. Heart wall tension reduction apparatus
US20040133063A1 (en) 1997-01-02 2004-07-08 Myocor Methods and devices for improving cardiac function in hearts
US20040167374A1 (en) 1997-01-02 2004-08-26 Myocor, Inc. Heart wall tension reduction apparatus and method
US20040267083A1 (en) 1997-01-02 2004-12-30 Myocor Methods and devices for improving cardiac function in hearts
US20020077524A1 (en) 1997-01-02 2002-06-20 Myocor, Inc. Heart wall tension reduction apparatus
US6045497A (en) 1997-01-02 2000-04-04 Myocor, Inc. Heart wall tension reduction apparatus and method
US20020058855A1 (en) 1997-01-02 2002-05-16 Myocor, Inc. Heart wall tension reduction apparatus and method
US6793618B2 (en) 1997-01-02 2004-09-21 Myocor, Inc. Heart wall tension reduction apparatus
US5928250A (en) 1997-01-30 1999-07-27 Nissho Corporation Catheter assembly for intracardiac suture
US6205747B1 (en) 1997-02-07 2001-03-27 Rosalina Paniagua Olaechea Process for closing nets for fruits and the like and net closed by means of said process
WO1998035632A1 (en) 1997-02-13 1998-08-20 Boston Scientific Ireland Limited Stabilization sling for use in minimally invasive pelvic surgery
USD399000S (en) 1997-03-11 1998-09-29 Cardiologic Systems, Inc. Vest for cardiopulmonary resuscitation and assist
US20020133055A1 (en) 1997-06-21 2002-09-19 Acorn Cardiovascular Inc. Bag for at least partially enveloping a heart
US6416459B1 (en) 1997-06-21 2002-07-09 Acorn Cardiovascular Inc. Bag for at least partially enveloping a heart
WO1998058598A1 (en) 1997-06-21 1998-12-30 Hans Haindl Bag for at least partially enveloping a heart
US6645139B2 (en) 1997-06-21 2003-11-11 Acorn Cardiovascular Inc. Bag for at least partially enveloping a heart
US6858001B1 (en) 1997-07-11 2005-02-22 A-Med Systems, Inc. Single port cardiac support apparatus
US5972013A (en) 1997-09-19 1999-10-26 Comedicus Incorporated Direct pericardial access device with deflecting mechanism and method
US20020029080A1 (en) 1997-12-17 2002-03-07 Myocor, Inc. Valve to myocardium tension members device and method
US6332893B1 (en) 1997-12-17 2001-12-25 Myocor, Inc. Valve to myocardium tension members device and method
US20040127983A1 (en) 1997-12-17 2004-07-01 Myocor, Inc. Valve to myocardium tension members device and method
US5839842A (en) 1998-02-05 1998-11-24 Lever Brothers Company, Division Of Conopco, Inc. Cleansing system including a toilet bar and sponge supported within a porous pouch
WO1999044534A1 (en) 1998-03-05 1999-09-10 The University Of Cincinnati Device and method for restructuring heart chamber geometry
US6190408B1 (en) 1998-03-05 2001-02-20 The University Of Cincinnati Device and method for restructuring the heart chamber geometry
US6409760B1 (en) 1998-03-05 2002-06-25 University Of Cincinnati Device and method for restructuring heart chamber geometry
US20040181120A1 (en) 1998-03-17 2004-09-16 Kochamba Gary S. Stabilizing tissue method and apparatus
US20040181118A1 (en) 1998-03-17 2004-09-16 Kochamba Gary S. Tissue stabilization
US20050059853A9 (en) 1998-03-17 2005-03-17 Kochamba Gary S. Tissue stabilization system
WO1999052470A1 (en) 1998-04-10 1999-10-21 Cardio Technologies, Inc. Cardiac remodeling and reinforcement device
US6095968A (en) 1998-04-10 2000-08-01 Cardio Technologies, Inc. Reinforcement device
WO1999052471A1 (en) 1998-04-11 1999-10-21 Intermedics Inc. Vascular and endoluminal stents with iridium oxide coating
US6494825B1 (en) 1998-04-22 2002-12-17 Scimed Life Systems, Inc. System for stress relieving the heart muscle and for controlling heart function
WO2000001306A1 (en) 1998-07-07 2000-01-13 Pulsecare Ltd. Minimal invasive cardiac massage device
US8277372B2 (en) 1998-07-13 2012-10-02 Mardil, Inc. Cardiac support device with differential compliance
US6997865B2 (en) 1998-07-13 2006-02-14 Acorn Cardiovascular, Inc. Cardiac support device with anti-fibrosis lining
US6123662A (en) 1998-07-13 2000-09-26 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6537203B1 (en) 1998-07-13 2003-03-25 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6582355B2 (en) 1998-07-13 2003-06-24 Acorn Cardiovascular, Inc. Cardiac disease treatment method
US20100160721A1 (en) 1998-07-13 2010-06-24 Acorn Cardiovascular, Inc. Cardiac support device with differential compliance
US6896652B2 (en) 1998-07-13 2005-05-24 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6085754A (en) 1998-07-13 2000-07-11 Acorn Cardiovascular, Inc. Cardiac disease treatment method
US7025719B2 (en) 1998-07-13 2006-04-11 Acorn Cardiovascular, Inc. Metallic cardiac support device
US7022064B2 (en) 1998-07-13 2006-04-04 Acorn Cardiovascular, Inc. Cardiac support with controlled ventricular pressure
WO2000002500A1 (en) 1998-07-13 2000-01-20 Acorn Cardiovascular, Inc. Cardiac disease treatment device and method
US20020169360A1 (en) 1998-07-16 2002-11-14 Cardiothoracic Systems, Inc., A California Corporation Surgical procedures and devices for increasing cardiac output of the heart
US6155968A (en) 1998-07-23 2000-12-05 Wilk; Peter J. Method and device for improving cardiac function
WO2000006028A9 (en) 1998-07-29 2000-08-10 Myocor Inc Transventricular implant tools and devices
US20010016675A1 (en) 1998-07-29 2001-08-23 Myocor, Inc. Stress reduction apparatus and method
US6264602B1 (en) 1998-07-29 2001-07-24 Myocor, Inc. Stress reduction apparatus and method
US6746471B2 (en) 1998-07-29 2004-06-08 Myocor, Inc. Transventricular implant tools and devices
US6260552B1 (en) 1998-07-29 2001-07-17 Myocor, Inc. Transventricular implant tools and devices
US20010025171A1 (en) 1998-07-29 2001-09-27 Myocor, Inc. Transventricular implant tools and devices
WO2000006026A9 (en) 1998-07-29 2000-08-10 Myocor Inc Heart wall tension reduction apparatus and method
WO2000006027A9 (en) 1998-07-29 2000-08-03 Myocor Inc Heart stress reduction apparatus and method
US20020173694A1 (en) 1998-07-29 2002-11-21 Myocor, Inc. Stress reduction apparatus and method
US20030032979A1 (en) 1998-07-29 2003-02-13 Myocor, Inc. Transventricular implant tools and devices
US6402680B2 (en) 1998-07-29 2002-06-11 Myocor, Inc. Stress reduction apparatus and method
US6077214A (en) 1998-07-29 2000-06-20 Myocor, Inc. Stress reduction apparatus and method
US6042536A (en) 1998-08-13 2000-03-28 Contimed, Inc. Bladder sling
US20050065396A1 (en) 1998-09-21 2005-03-24 Myocor, Inc. External stress reduction device and method
US6183411B1 (en) 1998-09-21 2001-02-06 Myocor, Inc. External stress reduction device and method
WO2000016700A1 (en) 1998-09-21 2000-03-30 Myocor, Inc. External stress reduction device and method
US20020169358A1 (en) 1998-09-21 2002-11-14 Myocor, Inc. External stress reduction device and method
US6402679B1 (en) 1998-09-21 2002-06-11 Myocor, Inc. External stress reduction device and method
US6808488B2 (en) 1998-09-21 2004-10-26 Myocor, Inc. External stress reduction device and method
US6558319B1 (en) 1998-09-30 2003-05-06 A-Med Systems, Inc. Heart stabilizer apparatus
US6685627B2 (en) 1998-10-09 2004-02-03 Swaminathan Jayaraman Modification of properties and geometry of heart tissue to influence heart function
US6360749B1 (en) 1998-10-09 2002-03-26 Swaminathan Jayaraman Modification of properties and geometry of heart tissue to influence heart function
US6876887B2 (en) 1998-11-04 2005-04-05 Acorn Cardiovascular, Inc. Cardio therapeutic heart sack
US6587734B2 (en) 1998-11-04 2003-07-01 Acorn Cardiovascular, Inc. Cardio therapeutic heart sack
US6230714B1 (en) 1998-11-18 2001-05-15 Acorn Cardiovascular, Inc. Cardiac constraint with prior venus occlusion methods
US6567699B2 (en) 1998-11-18 2003-05-20 Acorn Cardiovascular, Inc. Defibrillating cardiac constraint
WO2000028918A1 (en) 1998-11-18 2000-05-25 Acorn Cardiovascular, Inc. Defibrillating cardiac constraint
WO2000028912A1 (en) 1998-11-18 2000-05-25 Acorn Cardiovascular, Inc. Cardiac constraint with prior venus occlusion
US6370429B1 (en) 1998-11-18 2002-04-09 Acorn Cardiovascular, Inc. Defibrillating cardiac constraint
US6169922B1 (en) 1998-11-18 2001-01-02 Acorn Cardiovascular, Inc. Defibrillating cardiac jacket with interwoven electrode grids
US6432039B1 (en) 1998-12-21 2002-08-13 Corset, Inc. Methods and apparatus for reinforcement of the heart ventricles
US6076013A (en) 1999-01-14 2000-06-13 Brennan; Edward F. Apparatus and methods for treating congestive heart failure
US6155972A (en) 1999-02-02 2000-12-05 Acorn Cardiovascular, Inc. Cardiac constraint jacket construction
US6701929B2 (en) 1999-03-03 2004-03-09 Hany Hussein Device and method for treatment of congestive heart failure
US6695768B1 (en) 1999-03-30 2004-02-24 Robert A. Levine Adjustable periventricular ring/ring like device/method for control of ischemic mitral regurgitation and congestive heart disease
US6488618B1 (en) 1999-04-16 2002-12-03 Coroneo, Inc. Coronary stabilizer for performing beating heart surgery
US6709382B1 (en) 1999-05-04 2004-03-23 Simon Marcus Horner Cardiac assist method and apparatus
US20040147965A1 (en) 1999-06-07 2004-07-29 The Johns Hopkins University Cardiac shock electrode system and corresponding implantable defibrillator system
WO2001002500A1 (en) 1999-06-30 2001-01-11 Basf Coatings Ag Coating material and its use for producing filler coats and stone impact protection primers
US6727316B1 (en) 1999-06-30 2004-04-27 Basf Coatings Ag Coating material and its use for producing filler coats and stone impact protection primers
US6241654B1 (en) 1999-07-07 2001-06-05 Acorn Cardiovasculr, Inc. Cardiac reinforcement devices and methods
WO2001003608A1 (en) 1999-07-07 2001-01-18 Acorn Cardiovascular, Inc. Cardiac reinforcement devices and methods
WO2001010421A1 (en) 1999-08-06 2001-02-15 Board Of Regents, The University Of Texas System Drug releasing biodegradable fiber implant
US6852076B2 (en) 1999-08-09 2005-02-08 Cardiokinetix, Inc. Method for improving cardiac function
US20060229490A1 (en) 1999-08-10 2006-10-12 Chin Albert K Method for cardiac restaint
US7398781B1 (en) 1999-08-10 2008-07-15 Maquet Cardiovascular, Llc Method for subxiphoid endoscopic access
US6569082B1 (en) 1999-08-10 2003-05-27 Origin Medsystems, Inc. Apparatus and methods for cardiac restraint
US6179791B1 (en) 1999-09-21 2001-01-30 Acorn Cardiovascular, Inc. Device for heart measurement
US6174279B1 (en) 1999-09-21 2001-01-16 Acorn Cardiovascular, Inc. Cardiac constraint with tension indicator
US6193648B1 (en) 1999-09-21 2001-02-27 Acorn Cardiovascular, Inc. Cardiac constraint with draw string tensioning
US6541678B2 (en) 1999-09-27 2003-04-01 Brennen Medical, Inc. Immunostimulating coating for surgical devices
US6612978B2 (en) 1999-12-22 2003-09-02 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6702732B1 (en) 1999-12-22 2004-03-09 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6663558B2 (en) 1999-12-23 2003-12-16 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6881185B2 (en) 2000-01-14 2005-04-19 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US20040186342A1 (en) 2000-01-14 2004-09-23 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US20060155165A1 (en) 2000-01-14 2006-07-13 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US6579226B2 (en) 2000-01-14 2003-06-17 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US6689048B2 (en) 2000-01-14 2004-02-10 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US6293906B1 (en) 2000-01-14 2001-09-25 Acorn Cardiovascular, Inc. Delivery of cardiac constraint jacket
US6682474B2 (en) 2000-03-10 2004-01-27 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US7081086B2 (en) 2000-03-10 2006-07-25 Paracor Medical, Inc. Expandable cardiac harness for treating congestive heart failure
US7410461B2 (en) 2000-03-10 2008-08-12 Paracor Medical, Inc. Cardiac treatment apparatus
US6602184B2 (en) 2000-03-10 2003-08-05 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US6612979B2 (en) 2000-03-10 2003-09-02 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US20030065248A1 (en) 2000-03-10 2003-04-03 Lilip Lau Cardiac treatment apparatus
WO2001067985A1 (en) 2000-03-10 2001-09-20 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US20020019580A1 (en) 2000-03-10 2002-02-14 Lilip Lau Expandable cardiac harness for treating congestive heart failure
US20020045798A1 (en) 2000-03-10 2002-04-18 Lilip Lau Expandable cardiac harness for treating congestive heart failure
US20050020874A1 (en) 2000-03-10 2005-01-27 Lilip Lau Expandable cardiac harness for treating congestive heart failure
US7276022B2 (en) 2000-03-10 2007-10-02 Paracor Medical, Inc. Expandable cardiac harness for treating congestive heart failure
US6595912B2 (en) 2000-03-10 2003-07-22 Paracor Surgical, Inc. Expandable cardiac harness for treating congestive heart failure
US20030050529A1 (en) 2000-03-21 2003-03-13 Myocor, Inc. Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly
US6537198B1 (en) 2000-03-21 2003-03-25 Myocor, Inc. Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly
US6425856B1 (en) 2000-05-10 2002-07-30 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US7252632B2 (en) 2000-05-10 2007-08-07 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6908426B2 (en) 2000-05-10 2005-06-21 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
WO2001091667A9 (en) 2000-05-31 2002-07-04 Cardioclasp Inc Devices and methods for assisting natural heart function
US20050004428A1 (en) 2000-06-12 2005-01-06 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6902522B1 (en) 2000-06-12 2005-06-07 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6730016B1 (en) 2000-06-12 2004-05-04 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US20050085688A1 (en) 2000-06-13 2005-04-21 Acorn Cardiovascular, Inc. Cardiac support device
US6902524B2 (en) 2000-06-13 2005-06-07 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US8109868B2 (en) 2000-06-13 2012-02-07 Mardil, Inc. Cardiac support device
US20100185050A1 (en) 2000-06-13 2010-07-22 Acorn Cardiovascular, Inc. Compliant cardiac support device
US6482146B1 (en) 2000-06-13 2002-11-19 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
WO2001095830A8 (en) 2000-06-13 2003-11-06 Acorn Cardiovascular Inc Cardiac disease treatment and device
US20030229265A1 (en) 2000-06-13 2003-12-11 Girard Michael J. Cardiac support device
US20050228217A1 (en) 2000-06-13 2005-10-13 Acorn Cardiovascular, Inc. Compliant cardiac support device
US6682476B2 (en) 2000-06-13 2004-01-27 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6951534B2 (en) 2000-06-13 2005-10-04 Acorn Cardiovascular, Inc. Cardiac support device
WO2002000099A9 (en) 2000-06-23 2003-03-06 Viacor Inc Automated annular plication for mitral valve repair
WO2002013726A3 (en) 2000-08-17 2003-01-23 Acorn Cardiovascular Inc Cardiac disease treatment and device
US6572533B1 (en) 2000-08-17 2003-06-03 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US20070208211A1 (en) 2000-08-17 2007-09-06 Acorn Cardiovascular, Inc. Septum attached ventricular support
US20040215308A1 (en) 2000-09-18 2004-10-28 Cameron Health, Inc. Subcutaneous electrode with improved contact shape for transthoracic conduction
US6726920B1 (en) 2000-09-22 2004-04-27 Durect Corporation Implantable drug delivery patch
US20030233023A1 (en) 2000-09-23 2003-12-18 Harefield Cardiac Limited Blood circulation assistance device
US6776754B1 (en) 2000-10-04 2004-08-17 Wilk Patent Development Corporation Method for closing off lower portion of heart ventricle
US6723038B1 (en) 2000-10-06 2004-04-20 Myocor, Inc. Methods and devices for improving mitral valve function
US20050075723A1 (en) 2000-10-06 2005-04-07 Myocor, Inc. Methods and devices for improving mitral valve function
US6616684B1 (en) 2000-10-06 2003-09-09 Myocor, Inc. Endovascular splinting devices and methods
US20040225304A1 (en) 2000-10-06 2004-11-11 Myocor Endovascular splinting devices and methods
US20030181928A1 (en) 2000-10-06 2003-09-25 Myocor, Inc. Endovascular splinting devices and methods
US6673009B1 (en) 2000-11-08 2004-01-06 Acorn Cardiovascular, Inc. Adjustment clamp
US6616596B1 (en) 2000-11-28 2003-09-09 Abiomed, Inc. Cardiac assistance systems having multiple layers of inflatable elements
US6547716B1 (en) 2000-11-28 2003-04-15 Abiomed, Inc. Passive cardiac restraint systems having multiple layers of inflatable elements
US20020068850A1 (en) 2000-12-01 2002-06-06 Acorn Cardiovascular, Inc. Apparatus and method for delivery of cardiac constraint jacket
US6755779B2 (en) 2000-12-01 2004-06-29 Acorn Cardiovascular, Inc. Apparatus and method for delivery of cardiac constraint jacket
US6620095B2 (en) 2000-12-22 2003-09-16 Syde A. Taheri Cradle-assisted myocardial repair and treatment
US6564094B2 (en) 2000-12-22 2003-05-13 Acorn Cardiovascular, Inc. Cardiac disease treatment and device
US6575921B2 (en) 2001-02-09 2003-06-10 Acorn Cardiovascular, Inc. Device for heart measurement
US20040034272A1 (en) 2001-02-09 2004-02-19 Diaz Cesar M. Minimally invasive ventricular assist technology and method
US6622730B2 (en) 2001-03-30 2003-09-23 Myocor, Inc. Device for marking and aligning positions on the heart
US20020147406A1 (en) 2001-04-02 2002-10-10 Von Segesser Ludwig K. Cardiac stabilizers and methods of use thereof
US6726696B1 (en) 2001-04-24 2004-04-27 Advanced Catheter Engineering, Inc. Patches and collars for medical applications and methods of use
US6592514B2 (en) 2001-05-15 2003-07-15 Ethicon, Inc. Organ retraction tape positioner and method for retracting and positioning an internal organ
US7468029B1 (en) 2001-06-04 2008-12-23 Robertson Jr Abel L Progressive biventricular diastolic support device
US20040002626A1 (en) 2001-07-16 2004-01-01 Yair Feld In-vivo method and device for improving diastolic function of the left ventricle
US6716158B2 (en) 2001-09-07 2004-04-06 Mardil, Inc. Method and apparatus for external stabilization of the heart
US20030088149A1 (en) 2001-09-07 2003-05-08 Raman Jaishankar Method and apparatus for external stabilization of the heart
US20040267329A1 (en) 2001-09-07 2004-12-30 Mardil, Inc. Method and apparatus for external heart stabilization
WO2003022131A8 (en) 2001-09-07 2004-12-29 Mardil Inc Method and apparatus for external heart stabilization
US6723041B2 (en) 2001-09-10 2004-04-20 Lilip Lau Device for treating heart failure
US20050014992A1 (en) 2001-09-10 2005-01-20 Lau Lilip Device for treating heart failure
US6695769B2 (en) 2001-09-25 2004-02-24 The Foundry, Inc. Passive ventricular support devices and methods of using them
US7060023B2 (en) 2001-09-25 2006-06-13 The Foundry Inc. Pericardium reinforcing devices and methods of using them
US20030060895A1 (en) 2001-09-25 2003-03-27 French Ronald G. Pericardium reinforcing devices and methods of using them
US6755861B2 (en) 2001-10-16 2004-06-29 Granit Medical Innovation, Inc. Device for providing a portion of an organism with a desired shape
US20050033109A1 (en) 2001-10-31 2005-02-10 Lilip Lau Heart failure treatment device and method
US7404793B2 (en) 2001-10-31 2008-07-29 Paracor Medical, Inc. Heart failure treatment device and method
US20040147805A1 (en) 2002-01-07 2004-07-29 Lilip Lau Cardiac harness
US7022063B2 (en) 2002-01-07 2006-04-04 Paracor Medical, Inc. Cardiac harness
US7077862B2 (en) 2002-01-09 2006-07-18 Myocor, Inc. Devices and methods for heart valve treatment
US20030130731A1 (en) 2002-01-09 2003-07-10 Myocor, Inc. Devices and methods for heart valve treatment
US20040243229A1 (en) 2002-01-09 2004-12-02 Myocor, Inc. Devices and methods for heart valve treatment
US6764510B2 (en) 2002-01-09 2004-07-20 Myocor, Inc. Devices and methods for heart valve treatment
US7181272B2 (en) 2002-04-22 2007-02-20 Medtronic, Inc. Cardiac restraint with electrode attachment sites
US20040010180A1 (en) * 2002-05-16 2004-01-15 Scorvo Sean K. Cardiac assist system
US20030229260A1 (en) 2002-06-05 2003-12-11 Acorn Cardiovascular, Inc. Cardiac support device with tension indicator
US6682475B2 (en) * 2002-06-11 2004-01-27 Acorn Cardiovascular, Inc. Tension indicator for cardiac support device and method therefore
US20060063970A1 (en) 2002-09-06 2006-03-23 Mardil, Inc. Method and apparatus for external stabilization of the heart valves and myocardium
US20040133062A1 (en) 2002-10-11 2004-07-08 Suresh Pai Minimally invasive cardiac force transfer structures
US7112219B2 (en) 2002-11-12 2006-09-26 Myocor, Inc. Devices and methods for heart valve treatment
US20040210104A1 (en) 2002-11-15 2004-10-21 Lilip Lau Cardiac harness delivery device and method
US20050090707A1 (en) 2002-11-15 2005-04-28 Lilip Lau Cardiac harness delivery device and method
US20050256368A1 (en) 2002-11-15 2005-11-17 Paracor Medical, Inc. Introducer for a cardiac harness delivery
US20050059855A1 (en) 2002-11-15 2005-03-17 Lilip Lau Cardiac harness delivery device and method
US7189203B2 (en) 2002-11-15 2007-03-13 Paracor Medical, Inc. Cardiac harness delivery device and method
US20050010079A1 (en) 2002-12-06 2005-01-13 Estech, Inc. Methods and devices for cardiac surgery
US20040249242A1 (en) 2003-03-28 2004-12-09 Lilip Lau Multi-panel cardiac harness
US20050283042A1 (en) 2003-03-28 2005-12-22 Steve Meyer Cardiac harness having radiopaque coating and method of use
US20050054892A1 (en) 2003-07-10 2005-03-10 Lilip Lau Self-anchoring cardiac harness
US20050133941A1 (en) 2003-08-21 2005-06-23 Elringklinger Ag Tube with a marking and process for the production of a marking on a tube
US7235042B2 (en) 2003-09-16 2007-06-26 Acorn Cardiovascular, Inc. Apparatus and method for applying cardiac support device
US20070219407A1 (en) 2003-09-16 2007-09-20 Acorn Cardiovascular, Inc. Apparatus and method for applying cardiac support device
US20050059854A1 (en) 2003-09-16 2005-03-17 Acorn Cardiovascular, Inc. Apparatus and method for applying cardiac support device
US20080064917A1 (en) 2003-10-15 2008-03-13 Eli Bar Amplification-Based Cardiac Assist Device
US20050171589A1 (en) 2003-11-07 2005-08-04 Lilip Lau Cardiac harness and method of delivery by minimally invasive access
US7155295B2 (en) 2003-11-07 2006-12-26 Paracor Medical, Inc. Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing
US20060009831A1 (en) 2003-11-07 2006-01-12 Lilip Lau Cardiac harness having leadless electrodes for pacing and sensing therapy
US20050288715A1 (en) 2003-11-07 2005-12-29 Lilip Lau Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing
US20050192474A1 (en) 2004-03-01 2005-09-01 Acorn Cardiovascular, Inc. Seam closure device and methods
WO2006023580A3 (en) 2004-08-16 2007-04-12 Brigham & Womens Hospital Cardiac restraint
US20060270896A1 (en) 2005-05-31 2006-11-30 Ethicon, Inc. Method and device for deployment of a sub-pericardial sack
US20070032696A1 (en) 2005-07-22 2007-02-08 Sieu Duong Cardiac harness delivery device
US20070043416A1 (en) 2005-08-19 2007-02-22 Cardiac Pacemakers, Inc. Implantable electrode array
US20100268019A1 (en) 2006-03-03 2010-10-21 Acorn Cardiovascular, Inc. Cadiac support device delivery tool with independently movable arms
US20070208215A1 (en) 2006-03-03 2007-09-06 Acorn Cardiovascular, Inc. Self-adjusting securing structure for a cardiac support device
US20090131743A1 (en) 2006-06-29 2009-05-21 Acorn Cardiovascular, Inc. Low friction delivery tool for a cardiac support device
US8100821B2 (en) 2006-06-29 2012-01-24 Mardil, Inc. Low friction delivery tool for a cardiac support device
US7651462B2 (en) 2006-07-17 2010-01-26 Acorn Cardiovascular, Inc. Cardiac support device delivery tool with release mechanism
US20100094080A1 (en) 2006-07-17 2010-04-15 Acorn Cardiovascular, Inc. Cardiac support device delivery tool with release mechanism
US8202212B2 (en) 2006-07-17 2012-06-19 Mardil, Inc. Cardiac support device delivery tool with release mechanism
US20120253112A1 (en) 2006-07-17 2012-10-04 Mardil, Inc. Cardiac support device delivery tool with release mechanism
US8617051B2 (en) 2006-07-17 2013-12-31 Mardil, Inc. Cardiac support device delivery tool with release mechanism
US20080033234A1 (en) 2006-07-17 2008-02-07 Acorn Cardiovascular, Inc. Cardiac support device delivery tool with release mechanism
WO2008011411A2 (en) 2006-07-17 2008-01-24 Acorn Cardiovascular, Inc. Cardiac support device delivery tool with release mechanism
US8092363B2 (en) 2007-09-05 2012-01-10 Mardil, Inc. Heart band with fillable chambers to modify heart valve function
US20090062596A1 (en) 2007-09-05 2009-03-05 Leinsing Karl R Heart band with fillable chambers to modify heart valve function
US20100004504A1 (en) 2008-07-01 2010-01-07 Maquet Cardiovascular Llc Epicardial clip
WO2010111592A1 (en) 2009-03-27 2010-09-30 Acorn Cardiovascular, Inc. Intra-operative heart size measuring tool

Non-Patent Citations (30)

* Cited by examiner, † Cited by third party
Title
Bolling,et al., "Intermediate-Term Outcome of Mitral Reconstruction in Cardiomyopathy", J Thorac. Cardiovasc. Surg., Feb. 1998, 115(2):381-388.
Bourge, "Clinical Trial Begins for Innovative Device-Altering Left Ventricular Shape in Heart Failure", UAB Insight, posted Aug. 8, 2012, retrieved Jun. 17, 2004 , http://www.health.uab.edu/show, 2 pages.
Capomolla et al., "Dobutamine and nitroprusside infusion in patients with severe congestive heart failure: Hemodynamic improvement by discordant effects on mitral regurgitation, left atrial function, and ventricular function", American Heart Journal, Dec. 1997, 1089-1098.
Capouya et al., "Girdling Effect of Nonstimulated Cardiomyoplasty on Left Ventricular Function", Ann Thorac. Surg., 1993, 56:867-871.
Cohn, "The Management of Chronic Heart Failure", The New England Journal of Medicine, Aug. 15, 1996, 335(7): 490-498.
Coletta et al., "Prognostic value of left ventricular volume response during dobutamine stress echocardiography," European Heart Journal, Oct. 1997, 18: 1599-1605.
Daubeney et al., "Pulmonary Atresia/Intact Ventricular Septum: Early Outcome After Right Ventricular Outflow Reconstruction by Surgery or Catheter Intervention," Supplement to Circulation, Oct. 15, 1995, 92(8), Abstract 1812.
DeVries et al., "A Novel Technique for Measurement of Pericardial Balloon," Am. J Physiol Heart Circ Physiol, Jan. 2001, 280(6):H2815-H2822.
Ghanta, et al., "Cardiovascular Surgery: Adjustable, Physiological Ventricular Restraint Improves Left Ventricular Mechanics and Reduces Dilation in an Ovine Model of Chronic Heart Failure," Circulation, JAHA, 2007, 115:1201-10.
Guasp., "Una protesis contentiva para el tratamiento de la miocardiopatia dilatada," Revista Espanola de Cardiologia, Jul. 1998, 51(7): 521-528.
Hamilton et al., "Static and Dynamic Operating Characteristics of a Pericardial Balloon," J Appl. Physiol, Apr. 2001, 90(4):1481-1488.
Hung, et al., "Persistent Reduction of Ischemic Mitral Regurgitation by Papillary Muscle Repositioning: Structural Stabilization of the Pipillary Muscle Ventricular Wall Complex," Circulation, JAHA, 2007, 116:1-259 1-263.
International Search Report and Written Opinion in International Application No. PCT/US2013/064894, mailed Apr. 3, 2014, 27 pages.
International Search Report and Written Opinion in International Application No. PCT/US2013/064895, mailed Apr. 21, 2014, 14 pages.
Justo et al., "Outcomes of Transcatheter Perforation of the Right Ventricular Outflow Tract as Primary Management for Pulmonary Valve Atresia in the Newborn," Supplement to Circulation, Oct. 15, 1995, 92(8), Abstract 1813.
Kass et al., "Reverse Remodeling From Cardiomyoplasty in Human Heart Failure External Constraint Versus Active Assist," Circulation, May 1, 1995, 91(9):2314-2318, retrieved Jan. 16, 2014, http://circ.ahajournals.org/content/91/9/2314.full.
Labrousse, Louis et al., "Implantation of a Cardiac Support Device by the 'Parachute-Like' Technique Through Sternal and Trans-Abdominal Approach," Abstract, 94 Programme of the 4th EACTSIESTS Joint Meeting, Sep. 28, 2005, Barcelona, Spain.
Lamas, et al., "Clinical Significance of Mitral Regurgitation After Acute Myocardial Infarction," Circulation-JAHA, Aug. 5, 1997, 96(3):827-833, retrieved Jan. 16, 2014, http://circ.ahajournals.org/content/96/3/827.long.
Lei-Cohen, et al., "Design of a New Surgical Approach for Ventricular Remodeling to Relieve Ischemic Mitral Regurgitation," Circulation, Jun. 13, 2000, 101:2756-2763.
Levin et al., "Reversal of Chronic Ventricular Dilation in Patients with End-Stage Cardiomyopathy by Prolonged Mechanical Unloading," Circulation, Jun. 1, 1995, 91(11): 2717-2720, retrieved Jan. 16, 2014, http://circ.ahajournals.org/content/91/11/2717.long.
Lloyd et al., "The PDA Coil Registry: Report of the First 535 Procedures," Supplement to Circulation, Oct. 15, 1995, 92(8), Abstract 1811.
Oh et al., "The Effects of Prosthetic Cardiac Binding and Adynamic Cardiomyoplasty in a Model of Dilated Cardiomyopathy," The Journal of Thoracic and Cardiovascular Surgery, Jul. 1998, 116(1):148-153.
Pai, et al., "Valvular Egurgitation," Clinical Science Abstracts, 2000, 1800-1804.
Paling, "Two-Bar Fabrics (Part-Set Threading)", Warp Knitting Technology, Columbine Press (Publishers) Ltd., Buxton, Great Britain, p. III (1970).
Timek, et al., "Pathogenesis of Mitral Regurgitation in Tachycardia Induced Cardiomyopathy," Circulation-JAHA, 2001, 104:1-47-I-53.
U.S. Appl. No. 14/053,261, filed Oct. 16, 2013, Hjelle et al.
U.S. Appl. No. 14/053,590, filed Oct. 14, 2013, Hjelle et al.
U.S. Appl. No. 29/469,753, filed Oct. 14, 2013, Hjelle et al.
Vaynblat et al., "Cardiac Binding in Experimental Heart Failure," Ann. Thorac. Surg., 1994, vol. 64, 11 pages.
Vinereanu, et al., "'Pure' diastolic dysfunction is associated with long-axis systolic dysfunction. Implications for the diagnosis and classification of hear failure," European Journal of Heart Failure, Aug. 2005, 7(5): 820-828 (Abstract Only).

Also Published As

Publication number Publication date Type
US20140107405A1 (en) 2014-04-17 application
WO2014059432A3 (en) 2014-06-19 application
WO2014059433A3 (en) 2014-06-19 application
WO2014059432A2 (en) 2014-04-17 application
EP2906143A2 (en) 2015-08-19 application
CA2898620A1 (en) 2014-04-17 application
US20160331880A1 (en) 2016-11-17 application
US20140107775A1 (en) 2014-04-17 application
WO2014059433A2 (en) 2014-04-17 application
US20160262890A1 (en) 2016-09-15 application
US9421101B2 (en) 2016-08-23 grant
US9844437B2 (en) 2017-12-19 grant
JP2015536160A (en) 2015-12-21 application
EP2906151A4 (en) 2016-07-13 application
US9370425B2 (en) 2016-06-21 grant
US20160346085A1 (en) 2016-12-01 application
EP2906151A2 (en) 2015-08-19 application
EP2906143A4 (en) 2016-07-13 application
US20140107406A1 (en) 2014-04-17 application

Similar Documents

Publication Publication Date Title
US7297150B2 (en) Implantable devices for controlling the internal circumference of an anatomic orifice or lumen
US7186214B2 (en) Instruments and methods for accessing an anatomic space
US6149660A (en) Method and apparatus for delivery of an appliance in a vessel
US6126590A (en) Cardiac reinforcement device
US8070708B2 (en) Device and method for controlling in-vivo pressure
US6974476B2 (en) Percutaneous aortic valve
US6575921B2 (en) Device for heart measurement
US7815590B2 (en) Devices for maintaining patency of surgically created channels in tissue
US20060111692A1 (en) Robotically controlled intravascular tissue injection system
US20060217755A1 (en) Expandable guide sheath with steerable backbone and methods for making and using them
US8002740B2 (en) Devices for maintaining patency of surgically created channels in tissue
US20070173861A1 (en) System and method for positioning an artificial heart valve at the position of a malfunctioning valve of a heart through a percutaneous route
US20090149872A1 (en) Mitral valve treatment techniques
US20060135984A1 (en) Devices for maintaining patency of surgically created channels in tissue
US20070233238A1 (en) Devices for Imaging and Navigation During Minimally Invasive Non-Bypass Cardiac Procedures
US20070083187A1 (en) Apparatus and methods for delivering stem cells and other agents into cardiac tissue
US20100022948A1 (en) Steerable Catheter and Dilator and System and Method for Implanting a Heart Implant
US20090254103A1 (en) Method and device for cavity obliteration
US20080027483A1 (en) Implantable devices for controlling the size and shape of an anatomical structure or lumen
US20060195134A1 (en) Device, system, and method for aiding valve annuloplasty
US20070049971A1 (en) Method and apparatus for closing off a portion of a heart ventricle
US20040186368A1 (en) Systems and methods for internal tissue penetration
US20110118766A1 (en) Attachment System, Device and Method
US20110022168A1 (en) Post-operative adjustment tool, minimally invasive attachment apparatus, and adjustable tricuspid ring
US7699892B2 (en) Minimally invasive procedure for implanting an annuloplasty device

Legal Events

Date Code Title Description
AS Assignment

Owner name: MARDIL, INC., MINNESOTA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:HJELLE, AARON;COHN, WILLIAM E.;SCHROEDER, RICHARD F.;ANDOTHERS;SIGNING DATES FROM 20131115 TO 20131213;REEL/FRAME:032076/0063

CC Certificate of correction